Systems and methods for mid-processing calculation of blood composition

ABSTRACT

Blood separation methods are provided for mid-processing calculation of blood composition. Blood is conveyed into a device having an outlet line and the device is spun to separate platelets from the blood. A flow of platelets is conveyed from the device by the outlet line and the platelets in the outlet line are optically measured. With said optical measurement, a current platelet yield, a platelet pre-count, the volume of blood to process to collect a target amount of platelets, and/or the processing time required to collect a target amount of platelets is calculated. The optical measurement can also be used to calculate an amount of storage fluid to convey into a collection container with the platelets.

CROSS REFERENCE TO RELATED APPLICATIONS

This application claims priority from and the benefit of provisionalpatent application Ser. No. 61/031,987, filed Feb. 27, 2008, which ishereby incorporated herein by reference.

BACKGROUND

1. Field of the Disclosure

The present subject matter relates to systems and methods for processingand collecting blood, blood constituents, or other suspensions ofcellular material.

2. Description of Related Art

Today people routinely separate whole blood, usually by centrifugation,into its various therapeutic components, such as red blood cells,platelets, and plasma.

Conventional blood processing methods use durable centrifuge equipmentin association with single use, sterile processing systems, typicallymade of plastic. The operator loads the disposable systems upon thecentrifuge before processing and removes them afterwards.

Many conventional blood centrifuges are of a size that does not permiteasy transport between collection sites. Furthermore, loading andunloading operations can sometimes be time consuming and tedious.

In addition, a need exists for further improved systems and methods forcollecting blood components in a way that lends itself to use in avariety of applications, particularly, but not exclusively, where theoperational and performance demands upon such fluid processing systemsbecome more complex and sophisticated, even as the demand for smallerand more portable systems intensifies. The need therefore exists forautomated blood processing controllers that can gather and generate moredetailed information and control signals to aid the operator inmaximizing processing and separation efficiencies.

The present subject matter described below has particular, but notexclusive application, in portable blood processing systems, such asthose described in U.S. Pat. Nos. 6,348,156; 6,875,191; 7,011,761;7,087,177; and 7,297,272 and U.S. Patent Application Publication No.2005/0137516, which are hereby incorporated herein by reference, andsuch as embodied in the ALYX® blood processing systems marketed byFenwal, Inc. of Lake Zurich, Ill.

SUMMARY

There are several aspects of the present subject matter which may beembodied separately or together in the devices and systems described andclaimed below. These aspects may be employed alone or in combinationwith other aspects of the subject matter described herein, and thedescription of these aspects together is not intended to preclude theuse of these aspects separately or the claiming of such aspectsseparately as set forth in the claims appended hereto.

In one aspect, a blood separation method comprises processing blood in adevice to separate platelets from the blood and conveying fluidcontaining platelets from the device by an outlet line. The platelets inthe outlet line are optically measured. With said optical measurement, aplatelet pre-count is calculated. When the calculation is complete,additional blood is processed in the device.

In another separate aspect, a blood separation method comprisesprocessing blood in a device to separate platelets from the blood andcirculating a fluid containing platelets from the device through anoutlet line and then back into the device until the fluid issubstantially uniform. Simultaneously, the platelets in the outlet lineare optically measured and a current platelet yield, a plateletpre-count, the volume of blood to process to collect a target amount ofplatelets, and/or the processing time required to collect a targetamount of platelets is calculated, based at least in part on the opticalmeasurement of the platelets in the outlet line. After performing thecalculation, additional blood is processed in the device.

In yet another separate aspect, a blood separation method comprisesspinning a device to separate platelets from blood contained therein,conveying fluid containing platelets from the device by an outlet line,and optically measuring the platelets in the outlet line. A currentplatelet yield, a platelet pre-count, the volume of blood to process tocollect a target amount of platelets, and/or the processing timerequired to collect a target amount of platelets is calculated based atleast in part on the optical measurement. If current platelet yield iscalculated, it is compared to a target and, if the calculated yieldexceeds the target, the device is spun at a greater speed to reduce theamount of platelets in the outlet line. Alternatively, if the calculatedyield falls below the target, the device is spun at a slower speed toincrease the amount of platelets in the outlet line. After performingthe calculation, additional blood is processed in the device.

In yet another separate aspect, a blood separation method comprisesspinning a device at a separation speed sufficient to separate blood inthe device into a red blood cell layer, a plasma layer, and a layercontaining platelets. The separated plasma is conveyed from the devicethrough an outlet line thereof and the separated red blood cells areconveyed from the device through another outlet line, whilesubstantially all of the layer containing platelets is retained in thedevice. The device is then spun in alternating directions at arelatively low mixing speed to mix the separated plasma, the separatedred blood cells, and the layer containing platelets remaining in thedevice and then is spun at a harvest speed that is less than theseparation speed to separate the mixed plasma, red blood cells, andlayer containing platelets into a layer of red blood cells and a layercontaining plasma and platelets. The layer containing plasma andplatelets is conveyed from the device through one of the outlet linesand then back into the device to reduce the number of red blood cellsand leukocytes in the layer containing plasma and platelets. Theplatelets in the outlet line are optically measured while simultaneouslycirculating the layer containing plasma and platelets from the devicethrough the outlet line and then back into the device. A currentplatelet yield, a platelet pre-count, the volume of blood to process tocollect a target amount of platelets, and/or the processing timerequired to collect a target amount of platelets is calculated, based atleast in part on the optical measurement of the platelets in the outletline. After performing the calculation, additional blood is processed inthe device.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a blood or blood component processingsystem, with the disposable processing set of the system shown out ofassociation with the processing device prior to use;

FIG. 2 is a perspective view of the system shown in FIG. 1, with thedoors to the centrifuge station and pump and valve station being shownopen to accommodate mounting of the processing set;

FIG. 3 is a perspective view of the system shown in FIG. 1 with theprocessing set fully mounted on the processing device and ready for use;

FIG. 4 is a right perspective front view of the case that houses theprocessing device shown in FIG. 1, with the lid closed for transportingthe device;

FIG. 5 is a schematic view of a blood processing circuit, which can beprogrammed to perform a variety of different blood processing proceduresin association with the device shown in FIG. 1;

FIG. 6 is an exploded perspective view of a cassette, which contains theprogrammable blood processing circuit shown in FIG. 5, and the pump andvalve station on the processing device shown in FIG. 1, which receivesthe cassette for use;

FIG. 7 is a plane view of the front side of the cassette shown in FIG.6;

FIG. 8 is an enlarged perspective view of a valve station on thecassette shown in FIG. 6;

FIG. 9 is a plane view of the back side of the cassette shown in FIG. 6;

FIG. 10 is a plane view of a universal processing set, whichincorporates the cassette shown in FIG. 6, and which can be mounted onthe device shown in FIG. 1, as shown in FIGS. 2 and 3;

FIG. 11 is a top section view of the pump and valve station in which thecassette as shown in FIG. 6 is carried for use;

FIG. 12 is a schematic view of a pneumatic manifold assembly, which ispart of the pump and valve station shown in FIG. 6, and which suppliespositive and negative pneumatic pressures to convey fluid through thecassette shown in FIGS. 7 and 9;

FIG. 13 is a perspective front view of the case that houses theprocessing device, with the lid open for use of the device, and showingthe location of various processing elements housed within the case;

FIG. 14 is a schematic view of the controller that carries out theprocess control and monitoring functions of the device shown in FIG. 1;

FIGS. 15A, 15B, and 15C are schematic side views of the blood separationchamber that the device shown in FIG. 1 incorporates, showing the plasmaand red blood cell collection tubes and the associated two in-linesensors, which detect a normal operating condition (FIG. 15A), anoverspill condition (FIG. 15B), and an underspill condition (FIG. 15C);

FIG. 16 is a perspective view of a fixture that, when coupled to theplasma and red blood cell collection tubes, holds the tubes in a desiredviewing alignment with the in-line sensors, as shown in FIGS. 15A, 15B,and 15C;

FIG. 17 is a perspective view of the fixture shown in FIG. 16, with aplasma cell collection tube, a red blood cell collection tube, and awhole blood inlet tube attached, gathering the tubes in an organized,side-by-side array;

FIG. 18 is a perspective view of the fixture and tubes shown in FIG. 17,as being placed into viewing alignment with the two sensors shown inFIGS. 15A, 15B, and 15C;

FIG. 19 is a schematic view of the sensing station, of which the firstand second sensors shown in FIGS. 15A, 15B, and 15C form a part;

FIG. 20 is a graph of optical densities as sensed by the first andsecond sensors plotted over time, showing an underspill condition;

FIG. 21 is an exploded top perspective view of a molded centrifugalblood processing container, which can be used in association with thedevice shown in FIG. 1;

FIG. 22 is a bottom perspective view of the molded processing containershown in FIG. 21;

FIG. 23 is a top view of the molded processing container shown in FIG.21;

FIG. 24 is a side section view of the molded processing container shownin FIG. 21, showing an umbilicus to be connected to the container;

FIG. 24A is a top view of the connector that connects the umbilicus tothe molded processing container in the manner shown in FIG. 24, takengenerally along line 24A-24A in FIG. 24;

FIG. 25 is a side section view of the molded processing container shownin FIG. 24, after connection of the umbilicus to the container;

FIG. 26 is an exploded, perspective view of the centrifuge station ofthe processing device shown in FIG. 1, with the processing containermounted for use;

FIG. 27 is a further exploded, perspective view of the centrifugestation and processing container shown in FIG. 26;

FIG. 28 is a side section view of the centrifuge station of theprocessing device shown in FIG. 26, with the processing containermounted for use;

FIG. 29 is a top view of a molded centrifugal blood processing containeras shown in FIGS. 21 to 23, showing a flow path arrangement forseparating whole blood into plasma and red blood cells;

FIGS. 30 to 33 are top views of molded centrifugal blood processingcontainers as shown in FIGS. 21 to 23, showing other flow patharrangements for separating whole blood into plasma and red blood cells;

FIG. 34 is a schematic view of another blood processing circuit, whichcan be programmed to perform a variety of different blood processingprocedures in association with the device shown in FIG. 1;

FIG. 35 is a plane view of the front side of a cassette, which containsthe programmable blood processing circuit shown in FIG. 34;

FIG. 36 is a plane view of the back side of the cassette shown in FIG.35;

FIGS. 37A to 37E are schematic views of the blood processing circuitshown in FIG. 34, showing the programming of the cassette to carry outdifferent fluid flow tasks in connection with processing whole bloodinto plasma and red blood cells;

FIGS. 38A and 38B are schematic views of the blood processing circuitshown in FIG. 34, showing the programming of the cassette to carry outfluid flow tasks in connection with on-line transfer of an additivesolution into red blood cells separated from whole blood;

FIGS. 39A and 39B are schematic views of the blood processing circuitshown in FIG. 34, showing the programming of the cassette to carry outfluid flow tasks in connection with on-line transfer of red blood cellsseparated from whole blood through a filter to remove leukocytes;

FIG. 40 is a representative embodiment of a weigh scale suited for usein association with the device shown in FIG. 1;

FIG. 41 is a representative embodiment of another weigh scale suited foruse in association with the device shown in FIG. 1;

FIG. 42 is a schematic view of a flow rate sensing and control systemfor a pneumatic pump station employing an electrode to create anelectrical field inside the pump station;

FIG. 43 is a schematic view of a pneumatic manifold assembly, which ispart of the pump and valve station shown in FIG. 6, and which suppliespositive and negative pneumatic pressures to convey fluid through thecassette shown in FIGS. 35 and 36;

FIG. 44 is a top plan view of another embodiment of a blood processingchamber suitable for use with the blood processing systems and methodsof the present disclosure;

FIG. 45 is front perspective view of the blood processing chamber ofFIG. 44, with a portion thereof cut away for illustrative purposes;

FIG. 46 is a top plan view of the blood processing chamber of FIG. 44,illustrating the relative positions of separated blood components duringan exemplary blood component collection procedure;

FIG. 47 is a plane view of a disposable set, which can be mounted on thedevice shown in FIG. 1;

FIG. 48 is a plane view of another disposable set, which can be mountedon the device shown in FIG. 1;

FIG. 49 is a plane view of the front side of a cassette having fourteenports;

FIG. 50 is a plane view of the rear side of the cassette of FIG. 49;

FIG. 51 is a schematic view of a blood processing circuit defined by thecassette of FIGS. 49 and 50, which can be programmed to perform avariety of different blood processing procedures in association with thedevice shown in FIG. 1;

FIGS. 52A and 52B are schematic views of the blood processing circuit ofFIG. 51, showing the programming of the cassette to carry out differentfluid flow tasks in connection with drawing whole blood from a bloodsource;

FIG. 53 is a schematic view of the blood processing circuit of FIG. 51,showing the programming of the cassette to carry out different fluidflow tasks in connection with separating whole blood into constituentlayers;

FIGS. 54A-54C are schematic views of an interleaving process forreturning excess red blood cells and plasma to the blood source;

FIGS. 55A and 55B are schematic views of the blood processing circuit ofFIG. 51, showing the programming of the cassette to carry out differentfluid flow tasks in connection with establishing a target hematocrit inthe blood processing chamber;

FIGS. 56A and 56B are schematic views of the blood processing circuit ofFIG. 51, showing the programming of the cassette to carry out differentfluid flow tasks in connection with recombining the previously separatedblood components;

FIG. 57 is a schematic view of the blood processing circuit of FIG. 51,showing the programming of the cassette to carry out different fluidflow tasks in connection with priming the tubing leading to a plateletstorage solution container;

FIGS. 58A and 58B are schematic views of the blood processing circuit ofFIG. 51, showing the programming of the cassette to carry out differentfluid flow tasks in connection with re-separating the previouslyrecombined blood components;

FIG. 59A is a graphical representation of the recirculation rate (inml/min) versus the platelet concentration in a sample collected radiallyinward of the red blood cell and plasma interface which has beencollected after a predetermined period of recirculation;

FIG. 59B is a graphical representation of the recirculation rate (inml/min) versus the white blood cell count in a sample collected radiallyinward of the red blood cell and plasma interface which has beencollected after a predetermined period of recirculation;

FIG. 60A is a schematic view of the blood processing circuit of FIG. 51,showing the programming of the cassette to carry out different fluidflow tasks in connection with harvesting platelets using platelet poorplasma;

FIG. 60B is a schematic view of the blood processing circuit of FIG. 51,showing the programming of the cassette to carry out different fluidflow tasks in connection with harvesting platelets using a (non-plasma)platelet storage solution;

FIG. 61A is a graphical representation of white blood cell contaminationof a collected platelet product during a platelet harvesting stage;

FIGS. 61B-61D are graphical representations of processing chamber spinspeed profiles adapted to minimize the white blood cell contaminationillustrated in FIG. 61A;

FIG. 62 is a schematic view of the blood processing circuit of FIG. 51,showing the programming of the cassette to carry out different fluidflow tasks in connection with harvesting red blood cells;

FIGS. 63A-63D are schematic views of an automated burping procedure forremoving excess air from a flexible bag containing an amount of acollected blood component;

FIGS. 64A-64C are schematic views of the blood processing circuit ofFIG. 51, showing the programming of the cassette to carry out differentfluid flow tasks in connection with mixing packed red cells and anadditive solution;

FIG. 65 is a plane view of a disposable set, which can be mounted on thedevice shown in FIG. 1;

FIG. 66 is a plane view of another disposable set, which can be mountedon the device shown in FIG. 1;

FIGS. 67A-67E are schematic views of the blood processing circuit ofFIG. 51, showing the programming of the cassette to carry out differentfluid flow tasks in connection with collecting a separated bloodcomponent and flushing excess separated blood components from aprocessing system to a blood source;

FIG. 68 is a schematic view of the blood processing circuit of FIG. 51,showing the programming of the cassette to carry out different fluidflow tasks in connection with flushing blood components from aprocessing chamber; and

FIGS. 69A-69C are schematic views of the blood processing circuit ofFIG. 51, showing the programming of the cassette to carry out differentfluid flow tasks in connection with returning blood components from aprocessing chamber to a blood source.

DESCRIPTION OF THE ILLUSTRATED EMBODIMENTS

The embodiments disclosed herein are for the purpose of providing therequired description of the present subject matter. These embodimentsare only exemplary, and may be embodied in various forms. Therefore,specific details disclosed herein are not to be interpreted as limitingthe subject matter as defined in the accompanying claims.

FIG. 1 shows a fluid processing system 10 that embodies various aspectsof the present subject matter. The system 10 can be used for processingvarious fluids. The system 10 is particularly well suited for processingwhole blood and other suspensions of biological cellular materials.Accordingly, the illustrated embodiment shows the system 10 used forthis purpose.

I. System Overview

The system 10 includes three principal components. These are (i) aliquid and blood flow set 12; (ii) a blood processing device 14 thatinteracts with the flow set 12 to cause separation and collection of oneor more blood components; and (iii) a controller 16 that governs theinteraction to perform a blood processing and collection procedureselected by the operator.

A. The Processing Device and Controller

The blood processing device 14 and controller 16 are intended to bedurable items capable of long term use. In the illustrated embodiment,the blood processing device 14 and controller 16 are mounted inside aportable housing or case 36. The case 36 presents a compact footprint,suited for set up and operation upon a table top or other relativelysmall surface. The case 36 is also intended to be transported easily toa collection site.

The case 36 includes a base 38 and a hinged lid 40, which opens (as FIG.1 shows) and closes (as FIG. 4 shows). The lid 40 includes a latch 42,for releasably locking the lid 40 closed. The lid 40 also includes ahandle 44, which the operator can grasp for transporting the case 36when the lid 40 is closed. In use, the base 38 is intended to rest on agenerally horizontal support surface.

The case 36 can be formed into a desired configuration, e.g., bymolding. In one embodiment, the case 36 is made from a lightweight, yetdurable, plastic material.

B. The Flow Set

The flow set 12 is intended to be a sterile, single use, disposableitem. As FIG. 2 shows, before beginning a given blood processing andcollection procedure, the operator loads various components of the flowset 12 in the case 36 in association with the device 14. The controller16 implements the procedure based upon preset protocols, taking intoaccount other input from the operator. Upon completing the procedure,the operator removes the flow set 12 from association with the device14. The portions of the set 12 holding the collected blood component orcomponents are removed from the case 36 and retained for storage,transfusion, or further processing. The remainder of the set 12 isremoved from the case 36 and discarded.

The flow set 12 shown in FIG. 1 includes a blood processing chamber 18designed for use in association with a centrifuge. Accordingly, as FIG.2 shows, the processing device 14 includes a centrifuge station 20,which receives the processing chamber 18 for use. As FIGS. 2 and 3 show,the centrifuge station 20 comprises a compartment formed in the base 38.The centrifuge station 20 includes a door 22, which opens and closes thecompartment. The door 22 opens to allow loading of the processingchamber 18. The door 22 closes to enclose the processing chamber 18during operation.

The centrifuge station 20 rotates the processing chamber 18. Whenrotated, the processing chamber 18 centrifugally separates whole bloodreceived from a donor into component parts, e.g., red blood cells,plasma, and buffy coat comprising platelets and leukocytes.

It should also be appreciated that the system 10 need not separate bloodcentrifugally. The system 10 can accommodate other types of bloodseparation devices, e.g., a membrane blood separation device.

II. The Programmable Blood Processing Circuit

The set 12 defines a programmable blood processing circuit 46. Variousconfigurations are possible. FIG. 5 schematically shows onerepresentative configuration. FIG. 34 schematically shows anotherrepresentative configuration, which will be described later.

Referring to FIG. 5, the circuit 46 can be programmed to perform avariety of different blood processing procedures in which, e.g., redblood cells are collected, or plasma is collected, or both plasma andred blood cells are collected, or the buffy coat is collected.

The circuit 46 includes several pump stations PP(N), which areinterconnected by a pattern of fluid flow paths F(N) through an array ofin-line valves V(N). The circuit is coupled to the remainder of theblood processing set by ports P(N).

The circuit 46 includes a programmable network of flow paths, comprisingeleven universal ports P1 to P8 and P11 to P13 and three universal pumpstations PP1, PP2, and PP3. By selective operation of the in-line valvesV1 to V14, V16 to V18, and V21 to 23, any universal port P1 to P8 andP11 to P13 can be placed in flow communication with any universal pumpstation PP1, PP2, and PP3. By selective operation of the universalvalves, fluid flow can be directed through any universal pump station ina forward direction or reverse direction between two valves, or anin-out direction through a single valve.

In the illustrated embodiment, the circuit also includes an isolatedflow path comprising two ports P9 and P10 and one pump station PP4. Theflow path is termed “isolated,” because it cannot be placed into directflow communication with any other flow path in the circuit 46 withoutexterior tubing. By selective operation of the in-line valves V15, V19,and V20, fluid flow can be directed through the pump station in aforward direction or reverse direction between two valves, or an in-outdirection through a single valve.

The circuit 46 can be programmed to assign dedicated pumping functionsto the various pump stations. For example, in one embodiment, theuniversal pump station PP3 can serve as a general purpose, donorinterface pump, regardless of the particular blood procedure performed,to either draw blood from the donor or return blood or other fluid tothe donor through the port P8. In this arrangement, the pump station PP4can serve as a dedicated anticoagulant pump, to draw anticoagulant froma source through the port P10 and to meter anticoagulant into the bloodthrough port P9.

In this arrangement, the universal pump station PP1 can serve,regardless of the particular blood processing procedure performed, as adedicated in-process whole blood pump, to convey whole blood into theblood separator. This dedicated function frees the donor interface pumpPP3 from the added function of supplying whole blood to the bloodseparator. Thus, the in-process whole blood pump PP1 can maintain acontinuous supply of blood to the blood separator, while the donorinterface pump PP3 is simultaneously used to draw blood or return fluidto the donor through the single phlebotomy needle. Processing time isthereby minimized.

In this arrangement, the universal pump station PP2 can serve,regardless of the particular blood processing procedure performed, as aplasma pump, to convey plasma from the blood separator. The ability todedicate separate pumping functions provides a continuous flow of bloodand/or fluid into and out of the separator, as well as to and from thedonor.

The circuit 46 can be programmed, depending upon the objectives of theparticular blood processing procedure, to retain all or some of theplasma for storage or fractionation purposes, or to return all or someof the plasma to the donor. The circuit 46 can be further programmed,depending upon the objectives of the particular blood processingprocedure, to retain all or some of the red blood cells for storage, orto return all or some of the red blood cells to the donor. The circuit46 can also be programmed, depending upon the objectives of theparticular blood processing procedure, to retain all or some of thebuffy coat for storage, or to return all or some of the buffy coat tothe donor.

A. The Cassette

In one embodiment, the programmable fluid circuit 46 is implemented byuse of a fluid pressure actuated cassette 28 (see FIG. 6). The cassette28 provides a centralized, programmable, integrated platform for all thepumping and valving functions required for a given blood processingprocedure. In the illustrated embodiment, the fluid pressure comprisespositive and negative pneumatic pressure. Other types of fluid pressurecan be used.

As FIG. 6 shows, the cassette 28 interacts with a pneumatic actuatedpump and valve station 30, which is mounted in the lid 40 of the case 36(see FIG. 1). The cassette 28 is, in use, mounted in the pump and valvestation 30. The pump and valve station 30 applies positive and negativepneumatic pressure upon the cassette 28 to direct liquid flow throughthe circuit. Further details will be provided later.

The cassette 28 can take various forms. As illustrated (see FIG. 6), thecassette 28 comprises an injection molded body 188 having a front side190 and a back side 192. For the purposes of description, the front side190 is the side of the cassette 28 that, when the cassette 28 is mountedin the pump and valve station 30, faces away from the operator. Flexiblediaphragms 194 and 196 overlay both the front side 190 and the back side192 of the cassette 28, respectively.

The cassette body 188 is advantageously made of a rigid medical gradeplastic material. The diaphragms 194 and 196 are made of a flexiblematerial, for example, sheets of medical grade plastic. The diaphragms194 and 196 are sealed about their peripheries to the peripheral edgesof the front and back sides of the cassette body 188. Interior regionsof the diaphragms 194 and 196 can also be sealed to interior regions ofthe cassette body 188.

The cassette body 188 has an array of interior cavities formed on boththe front and back sides 190 and 192 (see FIGS. 7 and 9). The interiorcavities define the valve stations and flow paths shown schematically inFIG. 5. An additional interior cavity is provided in the back side ofthe cassette 28 to form a station that holds a filter material 200. Inthe illustrated embodiment, the filter material 200 comprises anovermolded mesh filter construction. The filter material 200 isintended, during use, to remove clots and cellular aggregations that canform during blood processing.

The pump stations PP1 to PP4 are formed as wells that are open on thefront side 190 of the cassette body 188. Upstanding edges peripherallysurround the open wells of the pump stations. The pump wells are closedon the back side 192 of the cassette body 188, except for a spaced pairof through holes or ports 202 and 204 for each pump station. The ports202 and 204 extend through to the back side 192 of the cassette body188. As will become apparent, either port 202 or 204 can serve itsassociated pump station as an inlet or an outlet, or both inlet andoutlet.

The in-line valves V1 to V23 are likewise formed as wells that are openon the front side 190 of the cassette. FIG. 8 shows a typical valveV(N). Upstanding edges peripherally surround the open wells of thevalves on the front side 190 of the cassette body 188. The valves areclosed on the back side 192 of the cassette 28, except that each valveincludes a pair of through holes or ports 206 and 208. One port 206communicates with a selected liquid path on the back side 192 of thecassette body 188. The other port 208 communicates with another selectedliquid path on the back side 192 of the cassette body 188.

In each valve, a valve seat 210 extends about one of the ports 208. Thevalve seat 210 is recessed below the surface of the recessed valve well,such that the port 208 is essentially flush with the surrounding surfaceof the recessed valve well, and the valve seat 210 extends below thesurface of the valve well.

The flexible diaphragm 194 overlying the front side 190 of the cassette28 rests against the upstanding peripheral edges surrounding the pumpstations and valves. With the application of positive force uniformlyagainst this side of the cassette body 188, the flexible diaphragm 194seats against the upstanding edges. The positive force forms peripheralseals about the pump stations and valves. This, in turn, isolates thepumps and valves from each other and the rest of the system. The pumpand valve station 30 applies positive force to the front side 190 of thecassette body 188 for this purpose.

Further localized application of positive and negative fluid pressuresupon the regions of the diaphragm 194 overlying these peripherallysealed areas serve to flex the diaphragm regions in these peripherallysealed areas. These localized applications of positive and negativefluid pressures on these diaphragm regions overlying the pump stationsserve to expel liquid out of the pump stations (with application ofpositive pressure) and draw liquid into the pump stations (withapplication of negative pressure).

In the illustrated embodiment, the bottom of each pump station PP1 toPP4 includes a recessed race 316 (see FIG. 7). The race 316 extendsbetween the ports 202 and 204, and also includes a dogleg extending atan angle from the top port 202. The race 316 provides better liquid flowcontinuity between the ports 202 and 204, particularly when thediaphragm region is forced by positive pressure against the bottom ofthe pump station. The race 316 also prevents the diaphragm region fromtrapping air within the pump station. Air within the pump station isforced into the race 316, where it can be readily venting through thetop port 202 out of the pump station, even if the diaphragm region isbottomed out in the station.

Likewise, localized applications of positive and negative fluid pressureon the diaphragm regions overlying the valves will serve to seat (withapplication of positive pressure) and unseat (with application ofnegative pressure) these diaphragm regions against the valve seats,thereby closing and opening the associated valve port. The flexiblediaphragm is responsive to an applied negative pressure for flexure outof the valve seat 210 to open the respective port. The flexiblediaphragm is responsive to an applied positive pressure for flexure intothe valve seat 210 to close and seal the respective port. When soflexed, the flexible diaphragm forms within the recessed valve seat 210a peripheral seal about the valve port 208.

In operation, the pump and valve station 30 applies localized positiveand negative fluid pressures to these regions of the front diaphragm 194for opening and closing the valve ports.

The liquid paths F1 to F35 are formed as elongated channels that areopen on the back side 192 of the cassette body 188, except for theliquid paths F15, F23, and F24 are formed as elongated channels that areopen on the front side 190 of the cassette body 188. The liquid pathsare shaded in FIG. 9 to facilitate their viewing. Upstanding edgesperipherally surround the open channels on the front and back sides 190and 192 of the cassette body 188.

The liquid paths F1 to F35 (except for liquid paths F15, F23, and F24)are closed on the front side 190 of the cassette body 188, except wherethe channels cross over valve station ports or pump station ports.Likewise, the liquid paths F15, F23, and F24 are closed on the back side192 of the cassette body 188, except where the channels cross overin-line ports communicating with certain channels on the back side 192of the cassette 28.

The flexible diaphragms 194 and 196 overlying the front and back sides190 and 192 of the cassette body 188 rest against the upstandingperipheral edges surrounding the liquid paths F1 to F35. With theapplication of positive force uniformly against the front and back sides190 and 192 of the cassette body 188, the flexible diaphragms 194 and196 seat against the upstanding edges. This forms peripheral seals alongthe liquid paths F1 to F35. In operation, the pump and valve station 30applies positive force to the diaphragms 194 and 196 for this purpose.

The pre-molded ports P1 to P13 extend out along two side edges of thecassette body 188. The cassette 28 is vertically mounted for use in thepump and valve station 30 (see FIG. 2). In this orientation, the portsP8 to P13 face downward, and the ports P1 to P7 are vertically stackedone above the other and face inward.

As FIG. 2 shows, the ports P8 to P13, by facing downward, are orientedwith container support trays 212 formed in the base 38, as will bedescribed later. The ports P1 to P7, facing inward, are oriented withthe centrifuge station 20 and a container weigh station 214, as willalso be described in greater detail later. The orientation of the portsP5 to P7 (which serve the processing chamber 18) below the ports P1 toP4 keeps air from entering the processing chamber 18.

This ordered orientation of the ports provides a centralized, compactunit aligned with the operative regions of the case 36.

B. The Universal Set

FIG. 10 schematically shows a universal set 264, which, by selectiveprogramming of the blood processing circuit 46 implemented by thecassette 28, is capable of performing several different blood processingprocedures.

The universal set 264 includes a donor tube 266, which is attached(through y-connectors 272 and 273) to tubing 300 having an attachedphlebotomy needle 268. The donor tube 266 is coupled to the port P8 ofthe cassette 28.

A container 275 for collecting an in-line sample of blood drawn throughthe tube 300 is also attached through the y-connector 273.

An anticoagulant tube 270 is coupled to the phlebotomy needle 268 viathe y-connector 272. The anticoagulant tube 270 is coupled to cassetteport P9. A container 276 holding anticoagulant is coupled via a tube 274to the cassette port P10. The anticoagulant tube 270 carries anexternal, manually operated in-line clamp 282 of conventionalconstruction.

A container 280 holding a red blood cell additive solution is coupledvia a tube 278 to the cassette port P3. The tube 278 also carries anexternal, manually operated in-line clamp 282.

A container 288 holding saline is coupled via a tube 284 to the cassetteport P12.

FIG. 10 shows the fluid holding containers 276, 280, and 288 as beingintegrally attached during manufacture of the set 264. Alternatively,all or some of the containers 276, 280, and 288 can be supplied separatefrom the set 264. The containers 276, 280, and 288 may be coupled byconventional spike connectors, or the set 264 may be configured toaccommodate the attachment of the separate container or containers atthe time of use through a suitable sterile connection, to therebymaintain a sterile, closed blood processing environment. Alternatively,the tubes 274, 278, and 284 can carry an in-line sterilizing filter anda conventional spike connector for insertion into a container port attime of use, to thereby maintain a sterile, closed blood processingenvironment.

The set 264 further includes tubes 290, 292, 294, which extend to anumbilicus 296. When installed in the processing station, the umbilicus296 links the rotating processing chamber 18 with the cassette 28without need for rotating seals. Further details of this constructionwill be provided later.

The tubes 290, 292, and 294 are coupled, respectively, to the cassetteports P5, P6, and P7. The tube 290 conveys whole blood into theprocessing chamber 18. The tube 292 conveys plasma from the processingchamber 18. The tube 294 conveys red blood cells from the processingchamber 18.

A plasma collection container 304 is coupled by a tube 302 to thecassette port P3. The collection container 304 is intended, in use, toserve as a reservoir for plasma during processing.

A red blood cell collection container 308 is coupled by a tube 306 tothe cassette port P2. The collection container 308 is intended, in use,to receive a first unit of red blood cells for storage.

A whole blood reservoir 312 is coupled by a tube 310 to the cassetteport P1. The collection container 312 is intended, in use, to serve as areservoir for whole blood during processing. It can also serve toreceive a second unit of red blood cells for storage.

As shown in FIG. 10, no tubing is coupled to the utility cassette portP13 and buffy port P4.

C. The Pump and Valve Station

The pump and valve station 30 includes a cassette holder 216. The door32 is hinged to move with respect to the cassette holder 216 between theopened position, exposing the cassette holder 216 (shown in FIG. 6) andthe closed position, covering the cassette holder 216 (shown in FIG. 3).The door 32 also includes an over center latch 218 with a latch handle220 (shown in FIG. 11). When the door 32 is closed, the latch 218 swingsinto engagement with the latch pin 222.

As FIG. 11 shows, the inside face of the door 32 carries an elastomericgasket 224. The gasket 224 contacts the back side 192 of the cassette 28when the door 32 is closed. An inflatable bladder 314 underlies thegasket 224.

With the door 32 opened (see FIG. 2), the operator can place thecassette 28 into the cassette holder 216. Closing the door 32 andsecuring the latch 218 brings the gasket 224 into facing contact withthe diaphragm 196 on the back side 192 of the cassette 28. Inflating thebladder 314 presses the gasket 224 into intimate, sealing engagementagainst the diaphragm 196. The cassette 28 is thereby secured in atight, sealing fit within the cassette holder 216.

The inflation of the bladder 314 also fully loads the over center latch218 against the latch pin 222 with a force that cannot be overcome bynormal manual force against the latch handle 220. The door 32 issecurely locked and cannot be opened when the bladder 314 is inflated.In this construction, there is no need for an auxiliary lock-out deviceor sensor to assure against opening of the door 32 during bloodprocessing.

The pump and valve station 30 also includes a manifold assembly 226located in the cassette holder 216 (FIG. 12). The manifold assembly 226comprises a molded or machined plastic or metal body. The front side 194of the diaphragm is held in intimate engagement against the manifoldassembly 226 when the door 32 is closed and the bladder 314 inflated.

The manifold assembly 226 is coupled to a pneumatic pressure source 234,which supplies positive and negative air pressure. The pneumaticpressure source 234 is carried inside the lid 40 behind the manifoldassembly 226.

In the illustrated embodiment, the pressure source 234 comprises twocompressors C1 and C2. However, one or several dual-head compressorscould be used as well. As FIG. 12 shows, one compressor C1 suppliesnegative pressure through the manifold 226 to the cassette 28. The othercompressor C2 supplies positive pressure through the manifold 226 to thecassette 28.

As FIG. 12 shows, the manifold 226 contains four pump actuators PA1 toPA4 and twenty-three valve actuators VA1 to VA23. The pump actuators PA1to PA4 and the valve actuators VA1 to VA23 are mutually oriented to forma mirror image of the pump stations PP1 to PP4 and valve stations V1 toV23 on the front side 190 of the cassette 28.

As FIG. 12 also shows, each actuator PA1 to PA4 and VA1 to VA23 includesa port 228. The ports 228 convey positive or negative pneumaticpressures from the source in a sequence governed by the controller 16.These positive and negative pressure pulses flex the front diaphragm 194to operate the pump stations PP1 to PP4 and valve stations V1 to V23 inthe cassette 28. This, in turn, moves blood and processing liquidthrough the cassette 28.

In the illustrated embodiment, the cassette holder 216 includes anintegral elastomeric membrane 232 (see FIG. 6) stretched across themanifold assembly 226. The membrane 232 serves as the interface betweenthe manifold assembly 226 and the diaphragm 194 of the cassette 28, whenfitted into the holder 216. The membrane 232 may include one or moresmall through holes (not shown) in the regions overlying the pump andvalve actuators PA1 to PA4 and V1 to V23. The holes are sized to conveypneumatic fluid pressure from the manifold assembly 226 to the cassettediaphragm 194. Still, the holes are small enough to retard the passageof liquid. The membrane 232 forms a flexible splash guard across theexposed face of the manifold assembly 226.

The splash guard membrane 232 keeps liquid out of the pump and valveactuators PA1 to PA4 and VA1 to VA23, should the cassette diaphragm 194leak. The splash guard membrane 232 also serves as a filter to keepparticulate matter out of the pump and valve actuators of the manifoldassembly 226. The splash guard membrane 232 can be periodically wipedclean when cassettes 28 are exchanged.

The manifold assembly 226 includes an array of solenoid actuatedpneumatic valves, which are coupled in-line with the pump and valveactuators PA1 to PA4 and VA1 to VA23. The manifold assembly 226, underthe control of the controller 16, selectively distributes the differentpressure and vacuum levels to the pump and valve actuators PA(N) andVA(N). These levels of pressure and vacuum are systematically applied tothe cassette 28, to route blood and processing liquids.

Under the control of a controller 16, the manifold assembly 226 alsodistributes pressure levels to the door bladder 314 (already described),as well as to a donor pressure cuff (not shown) and to a donor lineoccluder 320.

As FIG. 1 shows, the donor line occluder 320 is located in the case 36,immediately below the pump and valve station 30, in alignment with theports P8 and P9 of the cassette 28. The donor line 266, coupled to theport P8, passes through the occluder 320. The anticoagulant line 270,coupled to the port P9, also passes through the occluder 320. Theoccluder 320 is a spring loaded, normally closed pinch valve, betweenwhich the lines 266 and 270 pass. Pneumatic pressure from the manifoldassembly 234 is supplied to a bladder (not shown) through a solenoidvalve. The bladder, when expanded with pneumatic pressure, opens thepinch valve, to thereby open the lines 266 and 270. In the absence ofpneumatic pressure, the solenoid valve closes and the bladder vents toatmosphere. The spring loaded pinch valve of the occluder 320 closes,thereby closing the lines 266 and 270.

The manifold assembly 226 maintains several different pressure andvacuum conditions, under the control of the controller 16. In theillustrated embodiment, the following multiple pressure and vacuumconditions are maintained:

(i) Phard, or Hard Pressure, and Pinpr, or In-Process Pressure are thehighest pressures maintained in the manifold assembly 226. Phard isapplied for closing cassette valves V1 to V23. Pinpr is applied to drivethe expression of liquid from the in-process pump PP1 and the plasmapump PP2. A typical pressure level for Phard and Pinpr in the context ofan exemplary embodiment is 500 mmHg.

(ii) Pgen, or General Pressure, is applied to drive the expression ofliquid from the donor interface pump PP3 and the anticoagulant pump PP4.A typical pressure level for Pgen in the context of an exemplaryembodiment is 150 mmHg.

(iii) Pcuff, or Cuff Pressure, is supplied to the donor pressure cuff. Atypical pressure level for Pcuff in the context of an exemplaryembodiment is 80 mmHg.

(iv) Vhard, or Hard Vacuum, is the deepest vacuum applied in themanifold assembly 226. Vhard is applied to open cassette valves V1 toV23. A typical vacuum level for Vhard in the context of an exemplaryembodiment is −350 mmHg.

(v) Vgen, or General Vacuum, is applied to drive the draw function ofeach of the four pumps PP1 to PP4. A typical pressure level for Vgen inthe context of an exemplary embodiment is −300 mmHg.

(vi) Pdoor, or Door Pressure, is applied to the bladder 314 to seal thecassette 28 into the holder 216. A typical pressure level for Pdoor inthe context of an exemplary embodiment is 700 mmHg.

For each pressure and vacuum level, a variation of plus or minus 20mmHg, for example, is tolerated.

Pinpr is used to operate the in-process pump PP1, to pump blood into theprocessing chamber 18. The magnitude of Pinpr must be sufficient toovercome the pressure within the processing chamber 18, which may beapproximately 300 mmHg.

Similarly, Pinpr is used for the plasma pump PP2, since it must havesimilar pressure capabilities in the event that plasma needs to bepumped backwards into the processing chamber 18, e.g., during a spillcondition, as will be described later.

Pinpr and Phard are operated at the highest pressure to ensure thatupstream and downstream valves used in conjunction with pumping are notforced opened by the pressures applied to operate the pumps. Thecascaded, interconnectable design of the fluid paths F1 to F35 throughthe cassette 28 requires Pinpr-Phard to be the highest pressure applied.By the same token, Vgen is required to be less extreme than Vhard, toensure that pumps PP1 to PP4 do not overwhelm upstream and downstreamcassette valves V1 to V23.

Pgen is used to drive the donor interface pump PP3 and can be maintainedat a lower pressure, as can the AC pump PP4.

A main hard pressure line 322 and a main vacuum line 324 distributePhard and Vhard in the manifold assembly 226. The pressure and vacuumsources 234 run continuously to supply Phard to the hard pressure line322 and Vhard to the hard vacuum line 324.

A pressure sensor S1 monitors Phard in the hard pressure line 322. Thesensor S1 controls a solenoid SO38. The solenoid SO38 is normallyclosed. The sensor S1 opens the solenoid SO38 to build Phard up to itsmaximum set value. Solenoid SO38 is closed as long as Phard is withinits specified pressure range and is opened when Phard falls below itsminimum acceptable value.

Similarly, a pressure sensor S5 in the hard vacuum line 324 monitorsVhard. The sensor S5 controls a solenoid SO39. The solenoid SO39 isnormally closed. The sensor S5 opens the solenoid SO39 to build Vhard upto its maximum value. Solenoid SO39 is closed as long as Vhard is withinits specified pressure range and is opened when Vhard falls outside itsspecified range.

A general pressure line 326 branches from the hard pressure line 322. Asensor S2 in the general pressure line 326 monitors Pgen. The sensor S2controls a solenois SO30. The solenois SO30 is normally closed. Thesensor S2 opens the solenois SO30 to refresh Pgen from the hard pressureline 322, up to the maximum value of Pgen. Solenois SO30 is closed aslong as Pgen is within its specified pressure range and is opened whenPgen falls outside its specified range.

An in-process pressure line 328 also branches from the hard pressureline 322. A sensor S3 in the in-process pressure line 328 monitorsPinpr. The sensor S3 controls a solenois SO36. The solenois SO36 isnormally closed. The sensor S3 opens the solenois SO36 to refresh Pinprfrom the hard pressure line 322, up to the maximum value of Pinpr.Solenois SO36 is closed as long as Pinpr is within its specifiedpressure range and is opened when Pinpr falls outside its specifiedrange.

A general vacuum line 330 branches from the hard vacuum line 324. Asensor S6 monitors Vgen in the general vacuum line 330. The sensor S6controls a solenois SO31. The solenois SO31 is normally closed. Thesensor S6 opens the solenois SO31 to refresh Vgen from the hard vacuumline 324, up to the maximum value of Vgen. The solenois SO31 is closedas long as Vgen is within its specified range and is opened when Vgenfalls outside its specified range.

In-line reservoirs R1 to R5 are provided in the hard pressure line 322,the in-process pressure line 328, the general pressure line 326, thehard vacuum line 324, and the general vacuum line 330. The reservoirs R1to R5 assure that the constant pressure and vacuum adjustments as abovedescribed are smooth and predictable.

The solenoids SO33 and SO34 provide a vent for the pressures andvacuums, respectively, upon procedure completion. Since pumping andvalving will continually consume pressure and vacuum, the solenoids SO33and SO34 are normally closed. The solenoids SO33 and SO34 are opened tovent the manifold assembly upon the completion of a blood processingprocedure.

The solenoids SO28, SO29, SO35, SO37 and SO32 provide the capability toisolate the reservoirs R1 to R5 from the air lines that supply vacuumand pressure to the manifold assembly 226. This provides for muchquicker pressure/vacuum decay feedback, so that testing ofcassette/manifold assembly seal integrity can be accomplished. Thesesolenoids SO28, SO29, SO35, SO37, and SO32 are normally opened, so thatpressure cannot be built in the assembly 226 without a command to closethe solenoids SO28, SO29, SO35, SO37, and SO32, and, further, so thatthe system pressures and vacuums can vent in an error mode or with lossof power.

The solenoids SO1 to SO23 provide Phard or Vhard to drive the valveactuators VA1 to V23. In the unpowered state, these solenoids arenormally opened to keep all cassette valves V1 to V23 closed.

The solenoids SO24 and SO25 provide Pinpr and Vgen to drive thein-process and plasma pumps PP1 and PP2. In the unpowered state, thesesolenoids are opened to keep both pumps PP1 and PP2 closed.

The solenoids SO26 and SO27 provide Pgen and Vgen to drive the donorinterface and AC pumps PP3 and PP4. In the unpowered state, thesesolenoids are opened to keep both pumps PP3 and PP4 closed.

The solenois SO43 provides isolation of the door bladder 314 from thehard pressure line 322 during the procedure. The solenois SO43 isnormally opened and is closed when Pdoor is reached. A sensor S7monitors Pdoor and signals when the bladder pressure falls below Pdoor.The solenois SO43 is opened in the unpowered state to ensure bladder 314venting, as the cassette 28 cannot be removed from the holder while thedoor bladder 314 is pressurized.

The solenois SO42 provides Phard to open the safety occluder valve 320.Any error modes that might endanger the donor will relax (vent) thesolenoid SO42 to close the occluder 320 and isolate the donor.Similarly, any loss of power will relax the solenois SO42 and isolatethe donor.

The sensor S4 monitors Pcuff and communicates with solenois SO41 (forincreases in pressure) and solenois SO40 (for venting) to maintain thedonor cuff within its specified ranges during the procedure. Thesolenois SO40 is normally open so that the cuff line will vent in theevent of system error or loss of power. The solenois SO41 is normallyclosed to isolate the donor from any Phard in the event of power loss orsystem error.

FIG. 12 shows a sensor S8 in the pneumatic line serving the donorinterface pump actuator PA3. The sensor S8 is a bidirectional mass airflow sensor, which can monitor air flow to the donor interface pumpactuator PA3 to detect occlusions in the donor line. Alternatively, aswill be described in greater detail later, electrical field variationscan be sensed by an electrode carried within the donor interface pumpstation PP3, or any or all other pump stations PP1, PP2, or PP4, todetect occlusions, as well as to permit calculation of flow rates andthe detection of air.

Various alternative embodiments are possible. For example, the pressureand vacuum available to the four pumping stations could be modified toinclude more or less distinct levels or different groupings of “shared”pressure and vacuum levels. As another example, Vhard could be removedfrom access to the solenoids SO2, SO5, SO8, SO18, SO19, SO21, SO22 sincethe restoring springs will return the cassette valves to a closedposition upon removal of a vacuum. Furthermore, the vents shown asgrouped together could be isolated or joined in numerous combinations.

It should also be appreciated that any of the solenoids used in“normally open” mode could be re-routed pneumatically to be realized as“normally closed”. Similarly, any of the “normally closed” solenoidscould be realized as “normally open.”

As another example of an alternative embodiment, the hard pressurereservoir R1 could be removed if Pdoor and Phard were set to identicalmagnitudes. In this arrangement, the door bladder 314 could serve as thehard pressure reservoir. The pressure sensor S7 and the solenois SO43would also be removed in this arrangement.

III. Other Process Control Components of the System

As FIG. 13 best shows, the case 36 contains other components compactlyarranged to aid blood processing. In addition to the centrifuge station20 and pump and valve station 30, already described, the case 36includes a weigh station 238, an operator interface station 240, and oneor more trays 212 or hangers 248 for containers. The arrangement ofthese components in the case 36 can vary. In the illustrated embodiment,the weigh station 238, the controller 16, and the user interface station240, like the pump and valve station 30, are located in the lid 40 ofthe case 36. The holding trays 212 are located in the base 38 of thecase 36, adjacent the centrifuge station 20.

A. Container Support Components

The weigh station 238 comprises a series of container hangers/weighsensors 246 arranged along the top of the lid 40. In use (see FIG. 2),containers 304, 308, 312 are suspended on the hangers/weigh sensors 246.

The containers receive blood components separated during processing, aswill be described in greater detail later. The weigh sensors 246 provideoutput reflecting weight changes over time. This output is conveyed tothe controller 16. The controller 16 processes the incremental weightchanges to derive fluid processing volumes and flow rates. Thecontroller generates signals to control processing events based, inpart, upon the derived processing volumes. Further details of theoperation of the controller to control processing events will beprovided later.

The holding trays 212 comprise molded recesses in the base 38. The trays212 accommodate the containers 276 and 280 (see FIG. 2). In theillustrated embodiment, an additional swing-out hanger 248 is alsoprovided on the side of the lid 40. The hanger 248 (see FIG. 2) supportsthe container 288 during processing. In the illustrated embodiment, thetrays 212 and hanger 248 also include weigh sensors 246.

The weigh sensors 246 can be variously constructed. In the embodimentshown in FIG. 40, the scale includes a force sensor 404 incorporatedinto a housing 400, to which a hanger 402 is attached. The top surface420 of hanger 402 engages a spring 406 on the sensor 404. Another spring418 is compressed as a load, carried by the hanger 402, is applied. Thespring 418 resists load movement of the hanger 402, until the loadexceeds a predetermined weight (e.g., 2 kg.). At that time, the hanger402 bottoms out on mechanical stops 408 in the housing 400, therebyproviding over load protection.

In the embodiment shown in FIG. 41, a supported beam 410 transfers forceapplied by a hanger 416 to a force sensor 412 through a spring 414. Thisdesign virtually eliminates friction from the weight sensing system. Themagnitude of the load carried by the beam is linear in behavior, and theweight sensing system can be readily calibrated to ascertain an actualload applied to the hanger 416.

B. The Controller and Operator Interface Station

The controller 16 carries out process control and monitoring functionsfor the system 10. As FIG. 14 shows schematically, the controller 16comprises a main processing unit (MPU) 250, which can comprise, e.g., aPentium™ type microprocessor made by Intel Corporation, although othertypes of conventional microprocessors can be used. The controller 16 ismounted inside the lid 40 of the case 36 (as FIG. 13 shows).

In one embodiment, the MPU 250 employs conventional real timemulti-tasking to allocate MPU cycles to processing tasks. A periodictimer interrupt (for example, every 5 milliseconds) preempts theexecuting task and schedules another that is in a ready state forexecution. If a reschedule is requested, the highest priority task inthe ready state is scheduled. Otherwise, the next task on the list inthe ready state is scheduled.

As FIG. 14 shows, the MPU 250 includes an application control manager252. The application control manager 252 administers the activation of alibrary of at least one control application 254. Each controlapplication 254 prescribes procedures for carrying out given functionaltasks using the centrifuge station 20 and the pump and valve station 30in a predetermined way. In the illustrated embodiment, the applications254 reside as process software in EPROM's in the MPU 250.

The number of applications 254 can vary. In the illustrated embodiment,the applications 254 include at least one clinical procedureapplication. The procedure application contains the steps to carry outone prescribed clinical processing procedure. For the sake of example,in the illustrated embodiment, the application 254 includes threeprocedure applications: (1) a double unit red blood cell collectionprocedure; (2) a plasma collection procedure; and (3) a plasma/red bloodcell collection procedure. The details of these procedures will bedescribed later. Of course, additional procedure applications can beincluded.

As FIG. 14 shows, several slave processing units communicate with theapplication control manager 252. While the number of slave processingunits can vary, the illustrated embodiment shows five units 256(1) to256(5). The slave processing units 256(1) to 256(5), in turn,communicate with low level peripheral controllers 258 for controllingthe pneumatic pressures within the manifold assembly 226, the weighsensors 246, the pump and valve actuators PA1 to PA4 and VA1 to VA23 inthe pump and valve station 30, the motor for the centrifuge station 20,the interface sensing station 332, and other functional hardware of thesystem.

The MPU 250 contains in EPROM's the commands for the peripheralcontrollers 258, which are downloaded to the appropriate slaveprocessing unit 256(1) to 256(5) at start-up. The application controlmanager 252 also downloads to the appropriate slave processing unit256(1) to 256(5) the operating parameters prescribed by the activatedapplication 254.

With this downloaded information, the slave processing units 256(1) to256(5) proceed to generate device commands for the peripheralcontrollers 258, causing the hardware to operate in a specified way tocarry out the procedure. The peripheral controllers 258 return currenthardware status information to the appropriate slave processing unit256(1) to 256(5), which, in turn, generates the commands necessary tomaintain the operating parameters ordered by the application controlmanager 252.

In the illustrated embodiment, one slave processing unit 256(2) performsthe function of an environmental manager. The unit 256(2) receivesredundant current hardware status information and reports to the MPU 250should a slave unit malfunction and fail to maintain the desiredoperating conditions.

As FIG. 14 shows, the MPU 250 also includes an interactive userinterface 260, which allows the operator to view and comprehendinformation regarding the operation of the system 10. The interface 260is coupled to the interface station 240. The interface 260 allows theoperator to use the interface station 240 to select applications 254residing in the application control manager 252, as well as to changecertain functions and performance criteria of the system 10.

As FIG. 13 shows, the interface station 240 includes an interface screen262 carried in the lid 40. The interface screen 262 displays informationfor viewing by the operator in alpha-numeric format and as graphicalimages. In the illustrated embodiment, the interface screen 262 alsoserves as an input device. It receives input from the operator byconventional touch activation.

C. On-Line Monitoring of Pump Flows 1. Gravimetric Monitoring

Using the weigh scales 246, either upstream or downstream of the pumps,the controller 16 can continuously determine the actual volume of fluidthat is moved per pump stroke and correct for any deviations fromcommanded flow. The controller 16 can also diagnose exceptionalsituations, such as leaks and obstructions in the fluid path. Thismeasure of monitoring and control is desirable in an automated apheresisapplication, where anticoagulant has to be accurately metered with thewhole blood as it is drawn from the donor, and where product quality(e.g., hematocrit, plasma purity) is influenced by the accuracy of thepump flow rates.

The pumps PP1 to PP4 in the cassette 28 each provides arelatively-constant nominal stroke volume, or SV. The flow rate for agiven pump can therefore be expressed as follows:

$\begin{matrix}{Q = \frac{S\; V}{\left( {T_{Pump} + T_{Fill} + T_{Idle}} \right)}} & (1)\end{matrix}$where:

Q is the flow rate of the pump.

T_(Pump) is the time the fluid is moved out of the pump station.

T_(Fill) is the time the pump is filled with fluid.

T_(Idle) is the time when the pump is idle, that is, when no fluidmovement occurs.

The SV can be affected by the interaction of the pump with attacheddownstream and upstream fluid circuits. This is analogous, in electricalcircuit theory, to the interaction of a non-ideal current source withthe input impedance of the load it sees. Because of this, the actual SVcan be different than the nominal SV.

The actual fluid flow in volume per unit of time Q_(Actual) cantherefore be expressed as follows:

$\begin{matrix}{Q_{Actual} = {k \times \frac{S\; V_{Ideal}}{T_{Pump} + T_{Fill} + T_{Idle}}}} & (2)\end{matrix}$where:

Q_(Actual) is the actual fluid flow in volume per unit of time.

SV_(Ideal) is the theoretical stroke volume, based upon the geometry ofthe pump station. k is a correction factor that accounts for theinteractions between the pump and the upstream and downstream pressures.

The actual flow rate can be ascertained gravimetrically, using theupstream or downstream weigh scales 246, based upon the followingrelationship:

$\begin{matrix}{Q_{Actual} = \frac{\Delta\;{Wt}}{\rho \times \Delta\; T}} & (3)\end{matrix}$where:

ΔWt is the change in weight of fluid as detected by the upstream ordownstream weigh scale 246 during the time period ΔT.

ρ is the density of fluid.

ΔT is the time period where the change in weight ΔWt is detected in theweigh scale 246.

The following expression is derived by combining Equations (2) and (3):

$\begin{matrix}{k = {\left( {T_{Pump} + T_{Fill} + T_{Idle}} \right) \times \frac{\Delta\;{Wt}}{\left( {S\; V_{Ideal} \times \rho \times \Delta\; T} \right)}}} & (4)\end{matrix}$

The controller 16 computes k according to Equation (4) and then adjustsT_(Idle) so that the desired flow rate is achieved, as follows:

$\begin{matrix}{T_{Idle} = {\left( {k \times \frac{S\; V_{Ideal}}{Q_{Desired}}} \right) - T_{Pump} - T_{Fill}}} & (5)\end{matrix}$

The controller 16 updates the values for k and T_(Idle) frequently toadjust the flow rates.

Alternatively, the controller 16 can change T_(Pump) and/or T_(Fill)and/or T_(Idle) to adjust the flow rates.

In this arrangement, one or more of the time interval componentsT_(Pump), or T_(Fill), or T_(Idle) is adjusted to a new magnitude toachieve Q_(Desired), according to the following relationship:

$T_{n{({Adjusted})}} = {{k\left( \frac{S\; V_{Ideal}}{Q_{Desired}} \right)} - T_{n{({NotAdjusted})}}}$where:

T_(n(Adjusted)) is the magnitude of the time interval component orcomponents after adjustment to achieve the desired flow rateQ_(Desired).

T_(n(NotAdjusted)) is the magnitude of the value of the other timeinterval component or components of T_(Stroke) that are not adjusted.The adjusted stroke interval after adjustment to achieve the desiredflow rate Q_(Desired) is the sum of T_(n(Adjusted)) andT_(n(NotAdjusted)).

The controller 16 also applies the correction factor k as a diagnosticstool to determine abnormal operating conditions. For example, if kdiffers significantly from its nominal value, the fluid path may haveeither a leak or an obstruction. Similarly, if the computed value of kis of a polarity different from what was expected, then the direction ofthe pump may be reversed.

With the weigh scales 246, the controller 16 can perform on-linediagnostics even if the pumps are not moving fluid. For example, if theweigh scales 246 detect changes in weight when no flow is expected, thena leaky valve or a leak in the set 264 may be present.

In computing k and T_(Idle) and/or T_(Pump) and/or T_(Fill), thecontroller 16 may rely upon multiple measurements of ΔWt and/or ΔT. Avariety of averaging or recursive techniques (e.g., recursive least meansquares, Kalman filtering, etc.) may be used to decrease the errorassociated with the estimation schemes.

The above described monitoring technique is applicable for use for otherconstant stroke volume pumps, e.g. peristaltic pumps, etc.

2. Electrical Monitoring

In an alternative arrangement (see FIG. 42), the controller 16 includesa metal electrode 422 located in the chamber of each pump station PP1 toPP4 on the cassette 28. The electrodes 422 are coupled to a currentsource 424. The passage of current through each electrode 422 creates anelectrical field within the respective pump station PP1 to PP4.

Cyclic deflection of the diaphragm 194 to draw fluid into and expelfluid from the pump station PP1 to PP4 changes the electrical field,resulting in a change in total capacitance of the circuit through theelectrode 422. Capacitance increases as fluid is drawn into the pumpstation PP1 to PP4, and capacitance decreases as fluid is expelled fromthe pump station PP1 to PP4.

The controller 16 includes a capacitive sensor 426 (e.g., a QProx™ E2Ssensor from Quantum Research Group Ltd. of Hamble, England) coupled toeach electrode 422. The capacitive sensor 426 registers changes incapacitance for the electrode 422 in each pump station PP1 to PP4. Thecapacitance signal for a given electrode 422 has a high signal magnitudewhen the pump station is filled with liquid (diaphragm position 194 a),has a low signal magnitude signal when the pump station is empty offluid (diaphragm position 194 b), and has a range of intermediate signalmagnitudes when the diaphragm occupies positions between positions 194 aand 194 b.

At the outset of a blood processing procedure, the controller 16calibrates the difference between the high and low signal magnitudes foreach sensor to the maximum stroke volume SV of the respective pumpstation. The controller 16 then relates the difference between sensedmaximum and minimum signal values during subsequent draw and expelcycles to fluid volume drawn and expelled through the pump station. Thecontroller 16 sums the fluid volumes pumped over a sample time period toyield an actual flow rate.

The controller 16 compares the actual flow rate to a desired flow rate.If a deviance exists, the controller 16 varies pneumatic pressure pulsesdelivered to the actuator PA1 to PA4, to adjust T_(Idle) and/or T_(Pump)and/or T_(Fill) to minimize the deviance.

The controller 16 also operates to detect abnormal operating conditionsbased upon the variations in the electric field and to generate an alarmoutput. In the illustrated embodiment, the controller 16 monitors for anincrease in the magnitude of the low signal magnitude over time. Theincrease in magnitude reflects the presence of air inside a pumpstation.

In the illustrated embodiment, the controller 16 also generates aderivative of the signal output of the sensor 426. Changes in thederivative, or the absence of a derivative, reflects a partial orcomplete occlusion of flow through the pump station PP1 to PP4. Thederivative itself also varies in a distinct fashion depending uponwhether the occlusion occurs at the inlet or outlet of the pump stationPP1 to PP4.

IV. The Blood Processing Procedures A. Double RBC Collection Procedure(No Plasma Collection)

During this procedure, whole blood from a donor is centrifugallyprocessed to yield up to two units (approximately 500 ml) of red bloodcells for collection. All plasma constituent is returned to the donor.This procedure will, in shorthand, be called the double red blood cellcollection procedure.

Prior to undertaking the double red blood cell collection procedure, aswell as any blood collection procedure, the controller 16 operates themanifold assembly 226 to conduct an appropriate integrity check of thecassette 28, to determine whether there are any leaks in the cassette28. Once the cassette integrity check is complete and no leaks arefound, the controller 16 begins the desired blood collection procedure.

The double red blood cell collection procedure includes a pre-collectioncycle, a collection cycle, a post-collection cycle, and a storagepreparation cycle. During the pre-collection cycle, the set 264 isprimed to vent air prior to venipuncture. During the collection cycle,whole blood drawn from the donor is processed to collect two units ofred blood cells, while returning plasma to the donor. During thepost-collection cycle, excess plasma is returned to the donor, and theset is flushed with saline. During the storage preparation cycle, a redblood cell storage solution is added.

1. The Pre-Collection Cycle a. Anticoagulant Prime 1

In a first phase of the pre-collection cycle (AC Prime 1), tube 300leading to the phlebotomy needle 268 is clamped closed (see FIG. 10).The blood processing circuit 46 is programmed (through the selectiveapplication of pressure to the valves and pump stations of the cassette)to operate the donor interface pump PP3, drawing anticoagulant throughthe anticoagulant tube 270 and up the donor tube 266 through they-connector 272 (i.e., in through valve V13 and out through valve V11).The circuit is further programmed to convey air residing in theanticoagulant tube 270, the donor tube 266, and the cassette into thein-process container 312. This phase continues until an air detector 298along the donor tube 266 detects liquid, confirming the pumping functionof the donor interface pump PP3.

b. Anticoagulant Prime 2

In a second phase of the pre-collection cycle (AC Prime 2), the circuitis programmed to operate the anticoagulant pump PP4 to conveyanticoagulant into the in-process container 312. Weight changes in thein-process container 312. AC Prime 2 is terminated when theanticoagulant pump PP4 conveys a predetermined volume of anticoagulant(e.g., 10 g) into the in-process container 312, confirming its pumpingfunction.

c. Saline Prime 1

In a third phase of the pre-collection cycle (Saline Prime 1), theprocessing chamber 18 remains stationary. The circuit is programmed tooperate the in-process pump station PP1 to draw saline from the salinecontainer 288 through the in-process pump PP1. This creates a reverseflow of saline through the stationary processing chamber 18 toward thein-process container 312. In this sequence saline is drawn through theprocessing chamber 18 from the saline container 288 into the in-processpump PP1 through valve V14. The saline is expelled from the pump stationPP1 toward the in-process container 312 through valve V9. Weight changesin the saline container 288 are monitored. This phase is terminated uponregistering a predetermined weight change in the saline container 288,which indicates conveyance of a saline volume sufficient to initiallyfill about one half of the processing chamber 18 (e.g., about 60 g).

d. Saline Prime 2

With the processing chamber 18 about half full of priming saline, afourth phase of the pre-collection cycle begins (Saline Prime 2). Theprocessing chamber 18 is rotated at a low rate (e.g., about 300 RPM),while the circuit continues to operate in the same fashion as in SalinePrime 1. Additional saline is drawn into the pump station PP1 throughvalve V14 and expelled out of the pump station PP1 through valve V9 andinto the in-process container 312. Weight changes in the in-processcontainer 312 are monitored. This phase is terminated upon registering apredetermined weight change in the in-process container 312, whichindicates the conveyance of an additional volume of saline sufficient tosubstantially fill the processing chamber 18 (e.g., about 80 g).

e. Saline Prime 3

In a fifth phase of the pre-collection cycle (Saline Prime 3), thecircuit is programmed to first operate the in-process pump station PP1to convey saline from the in-process container 312 through all outletports of the separation device and back into the saline container 288through the plasma pump station PP2. This completes the priming of theprocessing chamber 18 and the in-process pump station PP1 (pumping inthrough valve V9 and out through valve V14), as well as primes theplasma pump station PP2, with the valves V7, V6, V10, and V12 opened toallow passive flow of saline. During this time, the rate at which theprocessing chamber 18 is rotated is successively ramped between zero and300 RPM. Weight changes in the in-process container 312 are monitored.When a predetermined initial volume of saline is conveyed in thismanner, the circuit is programmed to close valve V7, open valves V9 andV14, and to commence pumping saline to the saline container 288 throughthe plasma pump PP2, in through valve V12 and out through valve V10,allowing saline to passively flow through the in-process pump PP1.Saline in returned in this manner from the in-process container 312 tothe saline container 288 until weight sensing indicated that apreestablished minimum volume of saline occupies the in-processcontainer 312.

f. Vent Donor Line

In a sixth phase of the pre-collection cycle (Vent Donor Line), thecircuit is programmed to purge air from the venipuncture needle, priorto venipuncture, by operating the donor interface pump PP3 to pumpanticoagulant through anticoagulant pump PP4 and into the in-processcontainer 312.

g. Venipuncture

In a seventh phase of the pre-collection cycle (Venipuncture), thecircuit is programmed to close all valves V1 to V23, so thatvenipuncture can be accomplished.

The programming of the circuit during the phases of the pre-collectioncycle is summarized in the following table.

TABLE Programming of Blood Processing Circuit During Pre-CollectionCycle (Double Red Blood Cell Collection Procedure) Vent AC AC SalineSaline Saline Donor Veni- Phase Prime 1 Prime 2 Prime 1 Prime 2 Prime 3Line puncture V1 ● ● ● ● ● ● ● V2 ● ● ● ● ● ● ● V3 ◯ ◯ ● ● ● ◯ ● V4 ● ●◯ ◯ ● ● ● V5 ● ● ● ● ● ● ● V6 ● ● ● ● ◯ ● ● V7 ● ● ● ● ◯ ● ● (Stage 1) ●(Stage 2) V8 ● ● ● ● ● ● ● V9 ● ● ◯/● ◯/● ◯/● ● ● Pump Pump Pump In OutOut (Stage 1) ◯ (Stage 2) V10 ● ● ● ● ◯ ● ● (Stage 1) ◯/● Pump Out(Stage 2) V11 ◯/● ◯ ● ● ● ◯/● ● Pump Pump Out In V12 ● ● ● ● ◯ ● ●(Stage 1) ◯/● Pump In (Stage 2) V13 ◯/● ◯ ● ● ● ◯/● ● Pump In Pump OutV14 ● ● ◯/● ◯/● ◯/● ● ● Pump In Pump In Pump Out (Stage 1) ◯ (Stage 2)V15 ◯ ◯/● ● ● ● ◯ ● Pump Out V16 ● ● ● ● ● ● ● V17 ● ● ● ● ● ● ● V18 ◯ ◯● ● ● ◯ ● V19 ◯ ◯ ● ● ● ◯ ● V20 ◯ ◯/● ● ● ● ◯ ● Pump In V21 ● ● ● ● ● ●● V22 ● ● ◯ ◯ ◯ ● ● V23 ● ● ◯ ◯ ◯ ● ● PP1 ▪ ▪ □ □ □ ▪ ▪ (Stage 1) PP2 ▪▪ ▪ ▪ □ ▪ ▪ (Stage 2) PP3 □ ▪ ▪ ▪ ▪ □ ▪ PP4 ▪ □ ▪ ▪ ▪ ▪ ▪ Caption: ◯denotes an open valve; ● denotes a closed valve; ◯/● denotes a valveopening and closing during a pumping sequence; ▪ denotes an idle pumpstation (not in use); and □ denotes a pump station in use.

2. The Collection Cycle a. Blood Prime 1

With venipuncture, tube 300 leading to the phlebotomy needle 268 isopened. In a first phase of the collection cycle (Blood Prime 1), theblood processing circuit 46 is programmed (through the selectiveapplication of pressure to the valves and pump stations of the cassette)to operate the donor interface pump PP3 (i.e., in through valve V13 andout through valve V11) and the anticoagulant pump PP4 (i.e., in throughvalve V20 and out through valve V15) to draw anticoagulated bloodthrough the donor tube 270 into the in-process container 312. This phasecontinues until an incremental volume of anticoagulated whole bloodenters the in-process container 312, as monitored by the weigh sensor.

b. Blood Prime 2

In a next phase (Blood Prime 2), the blood processing circuit 46 isprogrammed to operate the in-process pump station PP1 to drawanticoagulated blood from the in-process container 312 through theseparation device. During this phase, saline displaced by the blood isreturned to the donor. This phase primes the separation device withanticoagulated whole blood. This phase continues until an incrementalvolume of anticoagulated whole blood leaves the in-process container312, as monitored by the weigh sensor.

c. Blood Separation While Drawing Whole Blood or Without Drawing WholeBlood

In a next phase of the blood collection cycle (Blood Separation WhileDrawing Whole Blood), the blood processing circuit 46 is programmed tooperate the donor interface pump station PP3 (i.e., in through valve V13and out through valve V11); the anticoagulant pump PP4 (i.e., in throughvalve V20 and out through valve V15); the in-process pump PP1 (i.e., inthrough valve V9 and out through valve V14); and the plasma pump PP2(i.e., in through valve V12 and out through valve V10). This arrangementdraws anticoagulated blood into the in-process container 312, whileconveying the blood from the in-process container 312 into theprocessing chamber for separation. This arrangement also removes plasmafrom the processing chamber into the plasma container 304, whileremoving red blood cells from the processing chamber into the red bloodcell container 308. This phase continues until an incremental volume ofplasma is collected in the plasma collection container 304 (as monitoredby the weigh sensor) or until a targeted volume of red blood cells iscollected in the red blood cell collection container (as monitored bythe weigh sensor).

If the volume of whole blood in the in-process container 312 reaches apredetermined maximum threshold before the targeted volume of eitherplasma or red blood cells is collected, the circuit is programmed foranother phase (Blood Separation Without Drawing Whole Blood), toterminate operation of the donor interface pump station PP3 (while alsoclosing valves V13, V11, V18, and V3) to terminate collection of wholeblood in the in-process container 312, while still continuing bloodseparation. If the volume of whole blood reaches a predetermined minimumthreshold in the in-process container 312 during blood separation, butbefore the targeted volume of either plasma or red blood cells iscollected, the circuit is programmed to return to the Blood SeparationWhile Drawing Whole Blood Phase, to thereby allow whole blood to enterthe in-process container 312. The circuit is programmed to togglebetween the Blood Separation While Drawing Whole Blood Phase and theBlood Separation Without Drawing Whole Blood Phase according to the highand low volume thresholds for the in-process container 312, until therequisite volume of plasma has been collected, or until the targetvolume of red blood cells has been collected, whichever occurs first.

d. Return Plasma and Saline

If the targeted volume of red blood cells has not been collected, thenext phase of the blood collection cycle (Return Plasma With Separation)programs the blood processing circuit 46 to operate the donor interfacepump station PP3 (i.e., in through valve V11 and out through valve V13);the in-process pump PP1 (i.e., in through valve V9 and out through valveV14); and the plasma pump PP2 (i.e., in through valve V12 and outthrough valve V10). This arrangement conveys anticoagulated whole bloodfrom the in-process container 312 into the processing chamber forseparation, while removing plasma into the plasma container 304 and redblood cells into the red blood cell container 308. This arrangement alsoconveys plasma from the plasma container 304 to the donor, while alsomixing saline from the container 288 in-line with the returned plasma.The in-line mixing of saline with plasma raises the saline temperatureand improves donor comfort. This phase continues until the plasmacontainer 304 is empty, as monitored by the weigh sensor.

If the volume of whole blood in the in-process container 312 reaches aspecified low threshold before the plasma container 304 empties, thecircuit is programmed to enter another phase (Return Plasma WithoutSeparation), to terminate operation of the in-process pump station PP1(while also closing valves V9, V10, V12, and V14) to terminate bloodseparation. The phase continues until the plasma container 304 empties.

e. Fill Donor Line

Upon emptying the plasma container 304, the circuit is programmed toenter a phase (Fill Donor Line), to operate the donor interface pumpstation PP3 (i.e., in through valve V11 and out through valve V13) todraw whole blood from the in-process container 312 to fill the donortube 266, thereby purging plasma (mixed with saline) in preparation foranother draw whole blood cycle.

The circuit is then programmed to conduct another Blood Separation WhileDrawing Whole Blood Phase, to refill the in-process container 312. Thecircuit is programmed in successive Blood Separation and Return PlasmaPhases until the weigh sensor indicates that a desired volume of redblood cells has been collected in the red blood cell collectioncontainer 308. When the targeted volume of red blood cells has beencollected, the post-collection cycle commences.

The programming of the circuit during the phases of the collection cycleis summarized in the following table.

TABLE Programming of Blood Processing Circuit During The CollectionCycle (Double Red Blood Cell Collection Procedure) Blood SeparationWhile Drawing Return Whole Blood Plasma/With (Without Separation FillBlood Blood Drawing (Without Donor Phase Prime 1 Prime 2 Whole Blood)Separation) Line V1 ● ● ● ● ◯ V2 ● ● ◯ ◯ ● (●) V3 ◯ ● ◯ ● ● (●) V4 ● ● ●● ● V5 ● ● ◯ ◯ ● V6 ● ● ● ◯/● ● Alternates With V23 V7 ● ◯ ● ● ◯ V8 ● ●● ● ● V9 ● ◯/● ◯/● ◯/● ● Pump In Pump In Pump In (●) V10 ● ● ◯/● ◯/● ●Pump Out Pump Out (●) V11 ◯/● ◯ ◯/● ◯/● ◯/● Pump Pump Out Pump In PumpIn Out (●) V12 ● ● ◯/● ◯/● ● Pump In Pump In (●) V13 ◯/● ◯ ◯/● ◯/● ◯/●Pump In Pump In Pump Out Pump Out (●) V14 ● ◯/● ◯/● ◯/● ● Pump Pump OutPump Out Out (●) V15 ◯/● ● ◯/● ● ● Pump Pump Out Out (●) V16 ● ● ● ● ●V17 ● ● ● ● ● V18 ◯ ◯ ◯ ◯ ◯ (●) V19 ◯ ● ◯ ● ● (●) V20 ◯/● ● ◯/● ● ● PumpIn Pump In (●) V21 ● ● ● ● ● V22 ● ● ● ◯ ● V23 ● ● ● ◯/● ● AlternatesWith V6 PP1 ▪ □ □ □ ▪ (▪) PP2 ▪ ▪ □ □ ▪ (▪) PP3 □ ▪ □ □ □ (▪) PP4 □ ▪ □▪ ▪ (▪) Caption: ◯ denotes an open valve; ● denotes a closed valve; ◯/●denotes a valve opening and closing during a pumping sequence; ▪ denotesan idle pump station (not in use); and □ denotes a pump station in use.

3. The Post-Collection Cycle

Once the targeted volume of red blood cells has been collected (asmonitored by the weigh sensor), the circuit is programmed to carry outthe phases of the post-collection cycle.

a. Return Excess Plasma

In a first phase of the post-collection cycle (Excess Plasma Return),the circuit is programmed to terminate the supply and removal of bloodto and from the processing chamber, while operating the donor interfacepump station PP3 (i.e., in through valve V11 and out through valve V13)to convey plasma remaining in the plasma container 304 to the donor. Thecircuit is also programmed in this phase to mix saline from thecontainer 288 in-line with the returned plasma. This phase continuesuntil the plasma container 304 is empty, as monitored by the weighsensor.

b. Saline Purge

In the next phase of the post-collection cycle (Saline Purge), thecircuit is programmed to operate the in-process pump station PP1 (i.e.,in through valve V14 and out through valve V9) to convey saline from thecontainer 288 through the separation device, to displace the bloodcontents of the separation device into the in-process container 312, inpreparation for their return to the donor. This phase reduces the lossof donor blood. This phase continues until a predetermined volume ofsaline is pumped through the separation device, as monitored by theweigh sensor.

c. Final Return to Donor

In the next phase of the post-collection cycle (Final Return), thecircuit is programmed to operate the donor interface pump station PP3(i.e., in through valve V11 and out through valve V13) to convey theblood contents of the in-process container 312 to the donor. Saline isintermittently mixed with the blood contents. This phase continues untilthe in-process container 312 is empty, as monitored by the weigh sensor.

d. Fluid Replacement

In the next phase (Fluid Replacement), the circuit is programmed tooperate the donor interface pump station PP3 (i.e., in through valve V11and out through valve V13) to convey the saline to the donor. This phasecontinues until a prescribed replacement volume amount is infused, asmonitored by the weigh sensor.

e. Empty In-Process Container

In the next phase of the post-collection cycle (Empty In-ProcessContainer), the circuit is programmed to operate the donor interfacepump station PP3 (i.e., in through valve V11 and out through valve V13)to convey all remaining contents of the in-process container 312 to thedonor, in preparation for splitting the contents of the red blood cellcontainer 308 for storage in both containers 308 and 312. This phasecontinues until a zero volume reading for the in-process container 312occurs, as monitored by the weigh sensor, and air is detected at the airdetector.

At this phase, the circuit is programmed to close all valves and idleall pump stations, so that the phlebotomy needle 268 can be removed fromthe donor.

The programming of the circuit during the phases of the post-collectioncycle is summarized in the following table.

TABLE Programming of Blood Processing Circuit During The Post-CollectionCycle (Double Red Blood Cell Collection Procedure) Excess Empty In-Plasma Saline Fluid Process Phase Return Purge Final Return ReplacementContainer V1 ● ● ◯ ● ◯ V2 ● ● ● ● ● V3 ● ● ● ● ● V4 ● ◯ ● ● ● V5 ◯ ● ● ●● V6 ◯/● ● ● ● ● Alternates With V23 V7 ● ● ◯/● ● ◯ Alternates With V23V8 ● ● ● ● ● V9 ◯ ◯/● ● ● ● Pump Out V10 ● ● ● ● ● V11 ◯/● ● ◯/● ◯/● ◯/●Pump In Pump In Pump In Pump In V12 ● ● ● ● ● V13 ◯/● ● ◯/● ◯/● ◯/● PumpOut Pump Out Pump Out Pump Out V14 ● ◯/● ● ● ● Pump In V15 ● ● ● ● ● V16● ● ● ● ● V17 ● ● ● ● ● V18 ◯ ● ◯ ◯ ◯ V19 ● ● ● ● ● V20 ● ● ● ● ● V21 ●● ● ● ● V22 ◯ ◯ ◯ ◯ ● V23 ◯/● ◯ ◯/● ◯ ● Alternates Alternates With WithV6 V7 PP1 ▪ □ ▪ ▪ ▪ PP2 ▪ ▪ ▪ ▪ ▪ PP3 □ ▪ □ □ □ PP4 ▪ ▪ ▪ ▪ ▪ Caption: ◯denotes an open valve; ● denotes a closed valve; ◯/● denotes a valveopening and closing during a pumping sequence; ▪ denotes an idle pumpstation (not in use); and □ denotes a pump station in use.

4. The Storage Preparation Cycle a. Split RBC

In the first phase of the storage preparation cycle (Split RBC), thecircuit is programmed to operate the donor interface pump station PP3 totransfer half of the contents of the red blood cell collection container308 into the in-process container 312. The volume pumped is monitored bythe weigh sensors for the containers 308 and 312.

b. Add RBC Preservative

In the next phases of the storage preparation cycle (Add StorageSolution to the In-Process Container and Add Storage Solution to the RedBlood Cell Collection Container), the circuit is programmed to operatethe donor interface pump station PP3 to transfer a desired volume of redblood cell storage solution from the container 280 first into thein-process container 312 and then into the red blood cell collectioncontainer 308. The transfer of the desired volume is monitored by theweigh scale.

c. End Procedure

In the next and final phase (End Procedure), the circuit is programmedto close all valves and idle all pump stations, so that the red bloodcell containers 308 and 312 can be separated and removed for storage.The remainder of the disposable set can now be removed and discarded.

The programming of the circuit during the phases of the storagepreparation cycle is summarized in the following table.

TABLE Programming of Blood Processing Circuit During The StoragePreparation Cycle (Double Red Blood Cell Collection Procedure) Split RBCEnd Between RBC Add Storage Procedure Collection And Solution To In- AddStorage (Remove In-Process Process Solution To RBC Veni- PhaseContainers Container Collection Container puncture) V1 ● ● ● ● V2 ◯ ● ◯● V3 ◯/● ◯ ● ● Alternates With V11 And V4 V4 ◯/● ● ◯ ● Alternates WithV11 And V3 V5 ● ● ● ● V6 ● ● ● ● V7 ● ● ● ● V8 ● ● ● ● V9 ● ● ● ● V10 ●● ● ● V11 ◯/● ◯/● ◯/● ● Pump In/ Pump In/ Pump In/ Pump Out Pump OutPump Out V12 ● ● ● ● V13 ● ● ● ● V14 ● ● ● ● V15 ● ● ● ● V16 ● ◯ ◯ ● V17● ● ● ● V18 ● ● ● ● V19 ● ● ● ● V20 ● ● ● ● V21 ● ◯ ◯ ● V22 ● ● ● ● V23● ● ● ● PP1 ▪ ▪ ▪ ▪ PP2 ▪ ▪ ▪ ▪ PP3 □ □ □ ▪ PP4 ▪ ▪ ▪ ▪ Caption: ◯denotes an open valve; ● denotes a closed valve; ◯/● denotes a valveopening and closing during a pumping sequence; ▪ denotes an idle pumpstation (not in use); and □ denotes a pump station in use.

B. Plasma Collection (No Red Blood Cell Collection)

During this procedure, whole blood from a donor is centrifugallyprocessed to yield up to 880 ml of plasma for collection. All red bloodcells are returned to the donor. This procedure will, in shorthand, becalled the plasma collection procedure.

Programming of the blood processing circuit 46 (through the selectiveapplication of pressure to the valves and pump stations of the cassette)makes it possible to use the same universal set 264 as in the double redblood cell collection procedure.

The procedure includes a pre-collection cycle, a collection cycle, and apost-collection cycle.

During the pre-collection cycle, the set 264 is primed to vent air priorto venipuncture. During the collection cycle, whole blood drawn from thedonor is processed to collect plasma, while returning red blood cells tothe donor. During the post-collection cycle, excess plasma is returnedto the donor, and the set is flushed with saline.

1. The Pre-Collection Cycle a. Anticoagulant Prime

In the pre-collection cycle for the plasma collection (no red bloodcells) procedure, the cassette is programmed to carry out AC Prime 1 andAC Prime 2 Phases that are identical to the AC Prime 1 and AC Prime 2Phases of the double red blood cell collection procedure.

b. Saline Prime/Vent Donor Line/Venipuncture

In the pre-collection cycle for the plasma collection (no red bloodcell) procedure, the cassette is programmed to carry out Saline Prime 1,Saline Prime 2, Saline Prime 3, Vent Donor Line, and Venipuncture Phasesthat are identical to the Saline Prime 1, Saline Prime 2, Saline Prime3, Vent Donor Line, and Venipuncture Phases of the double red blood cellcollection procedure.

The programming of the circuit during the phases of the pre-collectioncycle is summarized in the following table.

TABLE Programming of Blood Processing Circuit During Pre-CollectionCycle (Plasma Collection Procedure) Vent AC AC Saline Saline SalineDonor Veni- Phase Prime 1 Prime 2 Prime 1 Prime 2 Prime 3 Line punctureV1 ● ● ● ● ● ● ● V2 ● ● ● ● ● ● ● V3 ◯ ◯ ● ● ● ◯ ● V4 ● ● ◯ ◯ ● ● ● V5 ●● ● ● ● ● ● V6 ● ● ● ● ◯ ● ● V7 ● ● ● ● ◯ ● ● (Stage 1) ● (Stage 2) V8 ●● ● ● ● ● ● V9 ● ● ◯/● ◯/● ◯/● ● ● Pump Pump Pump In Out Out (Stage 1) ◯(Stage 2) V10 ● ● ● ● ◯ ● ● (Stage 1) ◯/● Pump Out (Stage 2) V11 ◯/● ◯ ●● ● ◯/● ● Pump Pump Out In V12 ● ● ● ● ◯ ● ● (Stage 1) ◯/● Pump In(Stage 2) V13 ◯/● ◯ ● ● ● ◯/● ● Pump In Pump Out V14 ● ● ◯/● ◯/● ◯/● ● ●Pump In Pump In Pump Out (Stage 1) ◯ (Stage 2) V15 ◯ ◯/● ● ● ● ◯ ● PumpOut V16 ● ● ● ● ● ● ● V17 ● ● ● ● ● ● ● V18 ◯ ◯ ● ● ● ◯ ● V19 ◯ ◯ ● ● ●◯ ● V20 ◯ ◯/● ● ● ● ◯ ● Pump In V21 ● ● ● ● ● ● ● V22 ● ● ◯ ◯ ◯ ● ● V23● ● ◯ ◯ ◯ ● ● PP1 ▪ ▪ □ □ □ ▪ ▪ (Stage 1) PP2 ▪ ▪ ▪ ▪ □ ▪ ▪ (Stage 2)PP3 □ ▪ ▪ ▪ ▪ □ ▪ PP4 ▪ □ ▪ ▪ ▪ ▪ ▪ Caption: ◯ denotes an open valve; ●denotes a closed valve; ◯/● denotes a valve opening and closing during apumping sequence; ▪ denotes an idle pump station (not in use); and □denotes a pump station in use.

2. The Collection Cycle a. Blood Prime 1

With venipuncture, the tube 300 leading to the phlebotomy needle 268 isopened. In a first phase of the collection cycle (Blood Prime 1), theblood processing circuit 46 is programmed to operate the donor interfacepump PP3 (i.e., in through valve V13 and out through valve V11) and theanticoagulant pump PP4 (i.e., in through valve V20 and out through valveV15) to draw anticoagulated blood through the donor tube 270 into thein-process container 312, in the same fashion as the Blood Prime 1 Phaseof the double red blood cell collection procedure, as already described.

b. Blood Prime 2

In a next phase (Blood Prime 2), the blood processing circuit 46 isprogrammed to operate the in-process pump station PP1 to drawanticoagulated blood from the in-process container 312 through theseparation device, in the same fashion as the Blood Prime 2 Phase forthe double red blood cell collection procedure, as already described.During this phase, saline displaced by the blood is returned to thedonor.

c. Blood Separation While Drawing Whole Blood or Without Drawing WholeBlood

In a next phase of the blood collection cycle (Blood Separation WhileDrawing Whole Blood), the blood processing circuit 46 is programmed tooperate the donor interface pump station PP3 (i.e., in through valve V13and out through valve V11); the anticoagulant pump PP4 (i.e., in throughvalve V20 and out through valve V15); the in-process pump PP1 (i.e., inthrough valve V9 and out through valve V14); and the plasma pump PP2(i.e., in through valve V12 and out through valve V10), in the samefashion as the Blood Separation While Drawing Whole Blood Phase for thedouble red blood cell collection procedure, as already described. Thisarrangement draws anticoagulated blood into the in-process container312, while conveying the blood from the in-process container 312 intothe processing chamber for separation. This arrangement also removesplasma from the processing chamber into the plasma container 304, whileremoving red blood cells from the processing chamber into the red bloodcell container 308. This phase continues until the targeted volume ofplasma is collected in the plasma collection container 304 (as monitoredby the weigh sensor) or until a targeted volume of red blood cells iscollected in the red blood cell collection container (as monitored bythe weigh sensor).

As in the double red blood cell collection procedure, if the volume ofwhole blood in the in-process container 312 reaches a predeterminedmaximum threshold before the targeted volume of either plasma or redblood cells is collected, the circuit is programmed to enter anotherphase (Blood Separation Without Drawing Whole Blood), to terminateoperation of the donor interface pump station PP3 (while also closingvalves V13, V11, V18, and V3) to terminate collection of whole blood inthe in-process container 312, while still continuing blood separation.If the volume of whole blood reaches a predetermined minimum thresholdin the in-process container 312 during blood separation, but before thetargeted volume of either plasma or red blood cells is collected, thecircuit is programmed to return to the Blood Separation While DrawingWhole Blood Phase, to thereby refill the in-process container 312. Thecircuit is programmed to toggle between the Blood Separation Phaseswhile drawing whole blood and without drawing whole blood, according tothe high and low volume thresholds for the in-process container 312,until the requisite volume of plasma has been collected, or until thetarget volume of red blood cells has been collected, whichever occursfirst.

d. Return Red Blood Cells/Saline

If the targeted volume of plasma has not been collected, the next phaseof the blood collection cycle (Return Red Blood Cells With Separation)programs the blood processing circuit 46 to operate the donor interfacepump station PP3 (i.e., in through valve V11 and out through valve V13);the in-process pump PP1 (i.e., in through valve V9 and out through valveV14); and the plasma pump PP2 (i.e., in through valve V12 and outthrough valve V10). This arrangement conveys anticoagulated whole bloodfrom the in-process container 312 into the processing chamber forseparation, while removing plasma into the plasma container 304 and redblood cells into the red blood cell container 308. This arrangement alsoconveys red blood cells from the red blood cell container 308 to thedonor, while also mixing saline from the container 288 in-line with thereturned red blood cells. The in-line mixing of saline with the redblood cells raises the saline temperature and improves donor comfort.The in-line mixing of saline with the red blood cells also lowers thehematocrit of the red blood cells being returned to the donor, therebyallowing a larger gauge (i.e., smaller diameter) phlebotomy needle to beused, to further improve donor comfort. This phase continues until thered blood cell container 308 is empty, as monitored by the weigh sensor.

If the volume of whole blood in the in-process container 312 reaches aspecified low threshold before the red blood cell container 308 empties,the circuit is programmed to enter another phase (Red Blood Cell ReturnWithout Separation), to terminate operation of the in-process pumpstation PP1 (while also closing valves V9, V10, V12, and V14) toterminate blood separation. The phase continues until the red blood cellcontainer 308 empties.

e. Fill Donor Line

Upon emptying the red blood cell container 308, the circuit isprogrammed to enter another phase (Fill Donor Line), to operate thedonor interface pump station PP3 (i.e., in through valve V11 and outthrough valve V13) to draw whole blood from the in-process container 312to fill the donor tube 266, thereby purging red blood cells (mixed withsaline) in preparation for another draw whole blood cycle.

The circuit is then programmed to conduct another Blood Separation WhileDrawing Whole Blood Phase, to refill the in-process container 312. Thecircuit is programmed to conduct successive draw whole blood and returnred blood cells/saline cycles, as described, until the weigh sensorindicates that a desired volume of plasma has been collected in theplasma collection container 304. When the targeted volume of plasma hasbeen collected, the post-collection cycle commences.

The programming of the circuit during the phases of the collection cycleis summarized in the following table.

TABLE Programming of Blood Processing Circuit During The CollectionCycle (Plasma Collection Procedure) Return Red Blood Separation BloodCells/ While Drawing Saline With Whole Blood Separation Blood Blood(Without Drawing (Without Fill Donor Phase Prime 1 Prime 2 Whole Blood)Separation) Line V1 ● ● ● ● ◯ V2 ● ● ◯ ◯ ● V3 ◯ ● ◯ ● ● (●) V4 ● ● ● ● ●V5 ● ● ◯ ◯ ● (●) V6 ● ● ● ● ● V7 ● ◯ ● ◯/● ◯ Alternates With V23 V8 ● ●● ● ● V9 ● ◯/● ◯/● ◯/● ● Pump In Pump In Pump In (●) V10 ● ● ◯/● ◯/● ●Pump Out Pump Out (●) V11 ◯/● ◯ ◯/● ◯/● ◯/● Pump Pump Out Pump In PumpIn Out (●) V12 ● ● ◯/● ◯/● ● Pump In Pump In (●) V13 ◯/● ◯ ◯/● ◯/● ◯/●Pump Pump In Pump Out Pump Out In (●) V14 ● ◯/● ◯/● ◯/● ● Pump Pump OutPump Out Out (●) V15 ◯/● ● ◯/● ● ● Pump Pump Out Out (●) V16 ● ● ● ● ●V17 ● ● ● ● ● V18 ◯ ◯ ◯ ◯ ◯ (●) V19 ◯ ● ◯ ● ● (●) V20 ◯/● ● ◯/● ● ● PumpPump In In (●) V21 ● ● ● ● ● V22 ● ● ● ◯ ● V23 ● ● ● ◯/● ● AlternatesWith V7 PP1 ▪ □ □ □ ▪ (▪) PP2 ▪ ▪ □ □ ▪ (▪) PP3 □ ▪ □ □ □ (▪) PP4 □ ▪ □▪ ▪ (▪) Caption: ◯ denotes an open valve; ● denotes a closed valve; ◯/●denotes a valve opening and closing during a pumping sequence; ▪ denotesan idle pump station (not in use); and □ denotes a pump station in use.

3. The Post-Collection Cycle

Once the targeted volume of plasma has been collected (as monitored bythe weigh sensor), the circuit is programmed to carry out the phases ofthe post-collection cycle.

a. Remove Plasma Collection Container

In a first phase of the post-collection cycle (Remove Plasma CollectionContainer), the circuit is programmed to close all valves and disableall pump stations to allow separation of the plasma collection container304 from the set 264.

b. Return Red Blood Cells

In the second phase of the post-collection cycle (Return Red BloodCells), the circuit is programmed to operate the donor interface pumpstation PP3 (i.e., in through valve V11 and out through valve V13) toconvey red blood cells remaining in the red blood cell collectioncontainer 308 to the donor. The circuit is also programmed in this phaseto mix saline from the container 288 in-line with the returned red bloodcells. This phase continues until the red blood cell container 308 isempty, as monitored by the weigh sensor.

c. Saline Purge

In the next phase of the post-collection cycle (Saline Purge), thecircuit is programmed to operate the in-process pump station PP1 (i.e.,in through valve V14 and out through valve V9) to convey saline from thecontainer 288 through the separation device, to displace the bloodcontents of the separation device into the in-process container 312, inpreparation for their return to the donor. This phase reduces the lossof donor blood. This phase continues until a predetermined volume ofsaline is pumped through the separation device, as monitored by theweigh sensor.

d. Final Return to Donor

In the next phase of the post-collection cycle (Final Return), thecircuit is programmed to operate the donor interface pump station PP3(i.e., in through valve V11 and out through valve V13) to convey theblood contents of the in-process container 312 to the donor. Saline isintermittently mixed with the blood contents. This phase continues untilthe in-process container 312 is empty, as monitored by the weigh sensor.

e. Fluid Replacement

In the next phase (Fluid Replacement), the circuit is programmed tooperate the donor interface pump station PP3 (i.e., in through valve V11and out through valve V13) to convey the saline to the donor. This phasecontinues until a prescribed replacement volume amount is infused, asmonitored by the weigh sensor.

f. End Procedure

In the final phase (End Procedure), the circuit is programmed to closeall valves and idle all pump stations, so that venipuncture can beterminated, and the plasma container can be separated and removed forstorage. The remaining parts of the disposable set can be removed anddiscarded.

The programming of the circuit during the phases of the post-collectioncycle is summarized in the following table.

TABLE Programming of Blood Processing Circuit During The Post-CollectionCycle (Plasma Collection Procedure) Remove Plasma Fluid End CollectionReturn Saline Final Replace- Proce- Phase Container RBC Purge Returnment dure V1 ● ● ● ◯ ● ● V2 ● ◯ ● ● ● ● V3 ● ● ● ● ● ● V4 ● ● ◯ ● ● ● V5● ● ● ● ● ● V6 ● ● ● ● ● ● V7 ● ◯/● ● ◯/● ● ● Alternates Alternates WithV23 With V23 V8 ● ● ● ● ● ● V9 ● ◯ ◯/● ● ● ● Pump Out V10 ● ● ● ● ● ●V11 ● ◯/● ● ◯/● ◯/● ● Pump In Pump In Pump In V12 ● ● ● ● ● ● V13 ● ◯/●● ◯/● ◯/● ● Pump Out Pump Out Pump Out V14 ● ● ◯/● ● ● ● Pump In V15 ● ●● ● ● ● V16 ● ● ● ● ● ● V17 ● ● ● ● ● ● V18 ◯ ◯ ● ◯ ◯ ● V19 ● ● ● ● ● ●V20 ● ● ● ● ● ● V21 ● ● ● ● ● ● V22 ● ◯ ◯ ◯ ◯ ● V23 ● ◯/● ◯ ◯/● ◯ ●Alternates Alternates With V7 With V7 PP1 ▪ ▪ □ ▪ ▪ ▪ PP2 ▪ ▪ ▪ ▪ ▪ ▪PP3 ▪ □ ▪ □ □ ▪ PP4 ▪ ▪ ▪ ▪ ▪ ▪ Caption: ◯ denotes an open valve; ●denotes a closed valve; ◯/● denotes a valve opening and closing during apumping sequence; ▪ denotes an idle pump station (not in use); and □denotes a pump station in use.

C. Red Blood Cell and Plasma Collection

During this procedure, whole blood from a donor is centrifugallyprocessed to collect up to about 550 ml of plasma and up to about 250 mlof red blood cells. This procedure will, in shorthand, be called the redblood cell/plasma collection procedure.

The portion of the red blood cells not retained for collection isperiodically returned to the donor during blood separation. Plasmacollected in excess of the 550 ml target and red blood cells collectedin excess of the 250 ml target are also returned to the donor at the endof the procedure.

Programming of the blood processing circuit 46 (through the selectiveapplication of pressure to the valves and pump stations of the cassette)makes it possible to use the same universal set 264 used to carry outthe double red blood cell collection or the plasma collection procedure.

The procedure includes a pre-collection cycle, a collection cycle, and apost-collection cycle, and a storage preparation cycle.

During the pre-collection cycle, the set 264 is primed to vent air priorto venipuncture. During the collection cycle, whole blood drawn from thedonor is processed to collect plasma and red blood cells, whilereturning a portion of the red blood cells to the donor. During thepost-collection cycle, excess plasma and red blood cells are returned tothe donor, and the set is flushed with saline. During the storagepreparation cycle, a red blood cell storage solution is added to thecollected red blood cells.

1 The Pre-Collection Cycle a. Anticoagulant Prime

In the pre-collection cycle for the red blood cell/plasma collectionprocedure, the cassette is programmed to carry out AC Prime 1 and ACPrime 2 Phases that are identical to the AC Prime 1 and AC Prime 2Phases of the double red blood cell collection procedure.

b. Saline Prime/Vent Donor Line/Venipuncture

In the pre-collection cycle for the red blood cell/plasma collectionprocedure, the cassette is programmed to carry out Saline Prime 1,Saline Prime 2, Saline Prime 3, Vent Donor Line, and Venipuncture Phasesthat are identical to the Saline Prime 1, Saline Prime 2, Saline Prime3, Vent Donor Line, and Venipuncture Phases of the double red blood cellcollection procedure.

The programming of the circuit during the phases of the pre-collectioncycle is summarized in the following table.

TABLE Programming of Blood Processing Circuit During Pre-CollectionCycle (Red Blood Cell/Plasma Collection Procedure) Vent AC AC SalineSaline Saline Donor Veni- Phase Prime1 Prime 2 Prime 1 Prime 2 Prime 3Line puncture V1 ● ● ● ● ● ● ● V2 ● ● ● ● ● ● ● V3 ◯ ◯ ● ● ● ◯ ● V4 ● ●◯ ◯ ● ● ● V5 ● ● ● ● ● ● ● V6 ● ● ● ● ◯ ● ● V7 ● ● ● ● ◯ ● ● (Stage 1) ●(Stage 2) V8 ● ● ● ● ● ● ● V9 ● ● ◯/● ◯/● ◯/● ● ● Pump Pump Pump In OutOut (Stage 1) ◯ (Stage 2) V10 ● ● ● ● ◯ ● ● (Stage 1) ◯/● Pump Out(Stage 2) V11 ◯/● ◯ ● ● ● ◯/● ● Pump Pump Out In V12 ● ● ● ● ◯ ● ●(Stage 1) ◯/● Pump In (Stage 2) V13 ◯/● ◯ ● ● ● ◯/● ● Pump In Pump OutV14 ● ● ◯/● ◯/● ◯/● ● ● Pump In Pump In Pump Out (Stage 1) ◯ (Stage 2)V15 ◯ ◯/● ● ● ● ◯ ● Pump Out V16 ● ● ● ● ● ● ● V17 ● ● ● ● ● ● ● V18 ◯ ◯● ● ● ◯ ● V19 ◯ ◯ ● ● ● ◯ ● V20 ◯ ◯/● ● ● ● ◯ ● Pump In V21 ● ● ● ● ● ●● V22 ● ● ◯ ◯ ◯ ● ● V23 ● ● ◯ ◯ ◯ ● ● PP1 ▪ ▪ □ □ □ ▪ ▪ (Stage 1) PP2 ▪▪ ▪ ▪ □ ▪ ▪ (Stage 2) PP3 □ ▪ ▪ ▪ ▪ □ ▪ PP4 ▪ □ ▪ ▪ ▪ ▪ ▪ Caption: ◯denotes an open valve; ● denotes a closed valve; ◯/● denotes a valveopening and closing during a pumping sequence; ▪ denotes an idle pumpstation (not in use); and □ denotes a pump station in use.

2. The Collection Cycle a. Blood Prime

With venipuncture, tube 300 leading to the phlebotomy needle 268 isopened. The collection cycle of the red blood cell/plasma collectionprocedure programs the circuit to carry out Blood Prime 1 and BloodPrime 2 Phases that are identical to the Blood Prime 1 and Blood Prime 2Phases of the Double Red Blood Cell Collection Procedure, alreadydescribed.

b. Blood Separation While Drawing Whole Blood or Without Drawing WholeBlood

In the blood collection cycle for the red blood cell/plasma collectionprocedure, the circuit is programmed to conduct a Blood Separation WhileDrawing Whole Blood Phase, in the same fashion that the Blood SeparationWhile Drawing Whole Blood Phase is conducted for the double red bloodcell collection procedure. This arrangement draws anticoagulated bloodinto the in-process container 312, while conveying the blood from thein-process container 312 into the processing chamber for separation.This arrangement also removes plasma from the processing chamber intothe plasma container 304, while removing red blood cells from theprocessing chamber into the red blood cell container 308. This phasecontinues until the desired maximum volumes of plasma and red bloodcells have been collected in the plasma and red blood cell collectioncontainers 304 and 308 (as monitored by the weigh sensor).

As in the double red blood cell collection procedure and the plasmacollection procedure, if the volume of whole blood in the in-processcontainer 312 reaches a predetermined maximum threshold before thetargeted volume of either plasma or red blood cells is collected, thecircuit is programmed to enter a phase (Blood Separation Without WholeBlood Draw) to terminate operation of the donor interface pump stationPP3 (while also closing valves V13, V11, V18, and V3) to terminatecollection of whole blood in the in-process container 312, while stillcontinuing blood separation. If the volume of whole blood reaches apredetermined minimum threshold in the in-process container 312 duringblood separation, but before the targeted volume of either plasma or redblood cells is collected, the circuit is programmed to return to theBlood Separation With Whole Blood Draw, to thereby refill the in-processcontainer 312. The circuit is programmed to toggle between the BloodSeparation cycle with whole blood draw and without whole blood drawaccording to the high and low volume thresholds for the in-processcontainer 312, until the requisite maximum volumes of plasma and redblood cells have been collected.

c. Return Red Blood Cells and Saline

If the targeted volume of plasma has not been collected, and red bloodcells collected in the red blood cell container 308 exceed apredetermined maximum threshold, the next phase of the blood collectioncycle (Return Red Blood Cells With Separation) programs the bloodprocessing circuit 46 to operate the donor interface pump station PP3(i.e., in through valve V11 and out through valve V13); the in-processpump PP1 (i.e., in through valve V9 and out through valve V14); and theplasma pump PP2 (i.e., in through valve V12 and out through valve V10).This arrangement continues to convey anticoagulated whole blood from thein-process container 312 into the processing chamber for separation,while removing plasma into the plasma container 304 and red blood cellsinto the red blood cell container 308. This arrangement also conveys allor a portion of the red blood cells collected in the red blood cellcontainer 308 to the donor. This arrangement also mixes saline from thecontainer 288 in-line with the returned red blood cells. The in-linemixing of saline with the red blood cells raises the saline temperatureand improves donor comfort. The in-line mixing of saline with the redblood cells also lowers the hematocrit of the red blood cells beingreturned to the donor, thereby allowing a larger gauge (i.e., smallerdiameter) phlebotomy needle to be used, to further improve donorcomfort.

This phase can continue until the red blood cell container 308 is empty,as monitored by the weigh sensor, thereby corresponding to the ReturnRed Blood Cells With Separation Phase of the plasma collectionprocedure. More advantageously, however, the processor determines howmuch additional plasma needs to be collected to meet the plasma targetvolume. From this, the processor derives the incremental red blood cellvolume associated with the incremental plasma volume. In thisarrangement, the processor returns a partial volume of red blood cellsto the donor, so that, upon collection of the next incremental red bloodcell volume, the total volume of red blood cells in the container 308will be at or slightly over the targeted red blood cell collectionvolume.

If the volume of whole blood in the in-process container 312 reaches aspecified low threshold before return of the desired volume of red bloodcells, the circuit is programmed to enter a phase (Return Red BloodCells Without Separation), to terminate operation of the in-process pumpstation PP1 (while also closing valves V9, V10, V12, and V14) toterminate blood separation. This phase corresponds to the Return RedBlood Cells Without Separation Phase of the plasma collection procedure.

d. Fill Donor Line

Upon returning the desired volume of red blood cells from the container308, the circuit is programmed to enter a phase (Fill Donor Line), tooperate the donor interface pump station PP3 (i.e., in through valve V11and out through valve V13) to draw whole blood from the in-processcontainer 312 to fill the donor tube 266, thereby purging red bloodcells (mixed with saline) in preparation for another draw whole bloodcycle.

The circuit is then programmed to conduct another Blood Separation WhileDrawing Whole Blood Phase, to refill the in-process container 312. Ifrequired, the circuit is capable of performing successive draw wholeblood and return red blood cells cycles, until the weigh sensorsindicate that volumes of red blood cells and plasma collected in thecontainers 304 and 308 are at or somewhat greater than the targetedvalues. The post-collection cycle then commences.

The programming of the circuit during the phases of the collection cycleis summarized in the following table.

TABLE Programming of Blood Processing Circuit During The CollectionCycle (Red Blood Cell/Plasma Collection Procedure) Return Red BloodSeparation Blood Cells/ While Drawing Saline With Whole Blood SeparationBlood Blood (Without Drawing (Without Fill Donor Phase Prime 1 Prime 2Whole Blood) Separation) Line V1 ● ● ● ● ◯ V2 ● ● ◯ ◯ ● V3 ◯ ● ◯ ● ● (●)V4 ● ● ● ● ● V5 ● ● ◯ ◯ ● (●) V6 ● ● ● ● ● V7 ● ◯ ● ◯/● ◯ AlternatesWith V23 V8 ● ● ● ● ● V9 ● ◯/● ◯/● ◯/● ● Pump In Pump In Pump In (●) V10● ● ◯/● ◯/● ● Pump Out Pump Out (●) V11 ◯/● ◯ ◯/● ◯/● ◯/● Pump Pump OutPump In Pump In Out (●) V12 ● ● ◯/● ◯/● ● Pump In Pump In (●) V13 ◯/● ◯◯/● ◯/● ◯/● Pump Pump In Pump Out Pump Out In (●) V14 ● ◯/● ◯/● ◯/● ●Pump Pump Out Pump Out Out (●) V15 ◯/● ● ◯/● ● ● Pump Pump Out Out (●)V16 ● ● ● ● ● V17 ● ● ● ● ● V18 ◯ ◯ ◯ ◯ ◯ (●) V19 ◯ ● ◯ ● ● (●) V20 ◯/●● ◯/● ● ● Pump Pump In In (●) V21 ● ● ● ● ● V22 ● ● ● ◯ ● V23 ● ● ● ◯/●● Alternates With V7 PP1 ▪ □ □ □ ▪ (▪) PP2 ▪ ▪ □ □ ▪ (▪) PP3 □ ▪ □ □ □(▪) PP4 □ ▪ □ ▪ ▪ (▪) Caption: ◯ denotes an open valve; ● denotes aclosed valve; ◯/● denotes a valve opening and closing during a pumpingsequence; ▪ denotes an idle pump station (not in use); and □ denotes apump station in use.

3. The Post-Collection Cycle

Once the targeted maximum volumes of plasma and red blood cells havebeen collected (as monitored by the weigh sensor), the circuit isprogrammed to carry out the phases of the post-collection cycle.

a. Return Excess Plasma

If the volume of plasma collected in the plasma collection container 304is over the targeted volume, a phase of the post-collection cycle(Excess Plasma Return) is entered, during which the circuit isprogrammed to terminate the supply and removal of blood to and from theprocessing chamber, while operating the donor interface pump station PP3(i.e., in through valve V11 and out through valve V13) to convey plasmain the plasma container 304 to the donor. The circuit is also programmedin this phase to mix saline from the container 288 in-line with thereturned plasma. This phase continues until the volume of plasma in theplasma collection container 304 is at the targeted value, as monitoredby the weigh sensor.

b. Return Excess Red Blood Cells

If the volume of red blood cells collected in the red blood cellcollection container 308 is also over the targeted volume, a phase ofthe post-collection cycle (Excess RBC Return) is entered, during whichthe circuit is programmed to operate the donor interface pump stationPP3 (i.e., in through valve V11 and out through valve V13) to convey redblood cells remaining in the red blood cell collection container 308 tothe donor. The circuit is also programmed in this phase to mix salinefrom the container 288 in-line with the returned red blood cells. Thisphase continues until the volume of red blood cells in the container 308equals the targeted value, as monitored by the weigh sensor.

c. Saline Purge

When the volumes of red blood cells and plasma collected in thecontainers 308 and 304 equal the targeted values, the next phase of thepost-collection cycle (Saline Purge) is entered, during which thecircuit is programmed to operate the in-process pump station PP1 (i.e.,in through valve V14 and out through valve V9) to convey saline from thecontainer 288 through the separation device, to displace the bloodcontents of the separation device into the in-process container 312, inpreparation for their return to the donor. This phase reduces the lossof donor blood. This phase continues until a predetermined volume ofsaline is pumped through the separation device, as monitored by theweigh sensor.

d. Final Return to Donor

In the next phase of the post-collection cycle (Final Return), thecircuit is programmed to operate the donor interface pump station PP3(i.e., in through valve V11 and out through valve V13) to convey theblood contents of the in-process container 312 to the donor. Saline isintermittently mixed with the blood contents. This phase continues untilthe in-process container 312 is empty, as monitored by the weigh sensor.

e. Fluid Replacement

In the next phase (Fluid Replacement), the circuit is programmed tooperate the donor interface pump station PP3 (i.e., in through valve V11and out through valve V13) to convey the saline to the donor. This phasecontinues until a prescribed replacement volume amount is infused, asmonitored by the weigh sensor.

f. End Venipuncture

In the next phase (End Venipuncture), the circuit is programmed to closeall valves and idle all pump stations, so that venipuncture can beterminated.

The programming of the circuit during the phases of the post-collectioncycle is summarized in the following table.

TABLE Programming of Blood Processing Circuit During The Post-CollectionCycle (Red Blood Cell/Plasma Collection Procedure) End Excess ExcessVeni- Plasma RBC Saline Final Fluid punc- Phase Return Return PurgeReturn Replacement ture V1 ● ● ● ◯ ● ● V2 ● ◯ ● ● ● ● V3 ● ● ● ● ● ● V4● ● ◯ ● ● ● V5 ◯ ● ● ● ● ● V6 ◯/● ● ● ● ● ● Alternates With V23 V7 ● ◯/●● ◯/● ● ● Alternates Alternates With V23 With V23 V8 ● ● ● ● ● ● V9 ◯ ◯◯/● ● ● ● Pump Out V10 ● ● ● ● ● ● V11 ◯/● ◯/● ● ◯/● ◯/● ● Pump In PumpIn Pump In Pump In V12 ● ● ● ● ● ● V13 ◯/● ◯/● ● ◯/● ◯/● ● Pump Out PumpOut Pump Out Pump Out V14 ● ● ◯/● ● ● ● Pump In V15 ● ● ● ● ● ● V16 ● ●● ● ● ● V17 ● ● ● ● ● ● V18 ◯ ◯ ● ◯ ◯ ● V19 ● ● ● ● ● ● V20 ● ● ● ● ● ●V21 ● ● ● ● ● ● V22 ◯ ◯ ◯ ◯ ◯ ● V23 ◯/● ◯/● ◯ ◯/● ◯ ● AlternatesAlternates Alternates With V6 With V7 With V7 PP1 ▪ ▪ □ ▪ ▪ ▪ PP2 ▪ ▪ ▪▪ ▪ ▪ PP3 □ □ ▪ □ □ ▪ PP4 ▪ ▪ ▪ ▪ ▪ ▪ Caption: ◯ denotes an open valve;● denotes a closed valve; ◯/● denotes a valve opening and closing duringa pumping sequence; ▪ denotes an idle pump station (not in use); and □denotes a pump station in use.

4. The Storage Preparation Cycle a. RBC Preservative Prime

In the first phase of the storage preparation cycle (Prime StorageSolution), the circuit is programmed to operate the donor interface pumpstation PP3 to transfer a desired volume of red blood cell storagesolution from the container 280 into the in-process container 312. Thetransfer of the desired volume is monitored by the weigh scale.

b. Transfer Storage Solution

In the next phase (Transfer Storage Solution), the circuit is programmedto operate the donor interface pump station PP3 to transfer a desiredvolume of red blood cell storage solution from the in-process container312 into the red blood cell collection container 308. The transfer ofthe desired volume is monitored by the weigh scale.

c. End Procedure

In the next and final phase (End Procedure), the circuit is programmedto close all valves and idle all pump stations, so that the plasma andred blood cell storage containers 304 and 308 can be separated andremoved for storage. The remainder of the disposable set can now beremoved and discarded.

The programming of the circuit during the phases of the storagepreparation cycle is summarized in the following table.

TABLE Programming of Blood Processing Circuit During The StoragePreparation Cycle (Red Blood Cell/Plasma Collection Procedure) PhasePrime Storage Solution Transfer Storage Solution End Procedure V1 ● ● ●V2 ● ◯ ● V3 ◯ ● ● V4 ● ◯ ● V5 ● ● ● V6 ● ● ● V7 ● ● ● V8 ● ● ● V9 ● ● ●V10 ● ● ● V11 ◯/● ◯/● ● Pump In/ Pump In/ Pump Out Pump Out V12 ● ● ●V13 ● ● ● V14 ● ● ● V15 ● ● ● V16 ◯ ◯ ● V17 ● ● ● V18 ● ● ● V19 ● ● ●V20 ● ● ● V21 ◯ ◯ ● V22 ● ● ● V23 ● ● ● PP1 ▪ ▪ ▪ PP2 ▪ ▪ ▪ PP3 □ □ ▪PP4 ▪ ▪ ▪ Caption: ◯ denotes an open valve; ● denotes a closed valve;◯/● denotes a valve opening and closing during a pumping sequence; ▪denotes an idle pump station (not in use); and □ denotes a pump stationin use.

V. Interface Control A. Underspill and Overspill Detection

In any of the above-described procedures, the centrifugal forces presentwithin the processing chamber 18 separate whole blood into a region ofpacked red blood cells and a region of plasma (see FIG. 15A). Thecentrifugal forces cause the region of packed red blood cells tocongregate along the outside or high-G wall of the chamber, while theregion of plasma is transported to the inside or low-G wall of thechamber.

An intermediate region forms an interface between the red blood cellregion and the plasma region. Intermediate density cellular bloodspecies like platelets and leukocytes populate the interface, arrangedaccording to density, with the platelets closer to the plasma layer thanthe leukocytes. The interface is also called the “buffy coat,” becauseof its cloudy color, compared to the straw color of the plasma regionand the red color of the red blood cell region.

It is desirable to monitor the location of the buffy coat, either tokeep the buffy coat materials out of the plasma or out of the red bloodcells, depending on the procedure, or to collect the cellular contentsof the buffy coat. The system includes a sensing station 332 comprisingtwo optical sensors 334 and 336 for this purpose.

In the illustrated embodiment of FIG. 13, the sensing station 332 islocated a short distance outside the centrifuge station 20. Thisarrangement minimizes the fluid volume of components leaving the chamberbefore monitoring by the sensing station 332.

The first sensor 334 in the station 332 optically monitors the passageof blood components through the plasma collection tube 292. The secondsensor 336 in the station 332 optically monitors the passage of bloodcomponents through the red blood cell collection tube 294.

The tubes 292 and 294 are made from plastic (e.g. polyvinylchloride)material that is transparent to the optical energy used for sensing, atleast in the region where the tubes 292 and 294 are to be placed intoassociation with the sensing station 332.

In the illustrated embodiment, the set 264 includes a fixture 338 (seeFIGS. 16 to 18) to hold the tubes 292 and 294 in viewing alignment withtheir respective sensor 334 and 336. The fixture 338 gathers the tubes292 and 294 in a compact, organized, side-by-side array, to be placedand removed as a group in association with the sensors 334 and 336,which are also arranged in a compact, side-by-side relationship withinthe station 332.

In the illustrated embodiment, the fixture 338 also holds the tube 290,which conveys whole blood into the centrifuge station 20, even though noassociated sensor is provided. The fixture 338 serves to gather and holdall tubes 290, 292, and 294 that are coupled to the umbilicus 296 in acompact and easily handled bundle.

The fixture 338 can be an integral part of the umbilicus 296, formed,e.g., by over molding. Alternatively, the fixture 338 can be aseparately fabricated part, which snap fits about the tubes 290, 292,and 294 for use.

In the illustrated embodiment (as FIG. 2 shows), the containers 304,308, and 312 coupled to the cassette 28 are suspended during use abovethe centrifugation station 20. In this arrangement, the fixture 338directs the tubes 290, 292, and 294 through an abrupt, ninety degreebend immediately beyond the end of the umbilicus 296 to the cassette 28.The bend imposed by the fixture 338 directs the tubes 290, 292, and 294in tandem away from the area immediately beneath the containers 304,308, and 312, thereby preventing clutter in this area. The presence ofthe fixture 338 to support and guide the tubes 290, 292, and 294 throughthe bend also reduces the risk of kinking or entanglement.

The first sensor 334 is capable of detecting the presence of opticallytargeted cellular species or components in the plasma collection tube292. The components that are optically targeted for detection varydepending upon the procedure.

For a plasma collection procedure, the first sensor 334 detects thepresence of platelets in the plasma collection tube 292, so that controlmeasures can be initiated to move the interface between the plasma andplatelet cell layer back into the processing chamber. This provides aplasma product that can be essentially platelet-free or at least inwhich the number of platelets is minimized.

For a red blood cell-only collection procedure, the first sensor 334detects the interface between the buffy coat and the red blood celllayer, so that control measures can be initiated to move this interfaceback into the processing chamber. This maximizes the red blood cellyield.

For a buffy coat collection procedure (which will be described later),the first sensor 334 detects when the leading edge of the buffy coat(i.e., the plasma/platelet interface) begins to exit the processingchamber, as well as detects when the trailing edge of the buffy coat(i.e., the buffy coat/red blood cell interface) has completely exitedthe processing chamber.

The presence of these cellular components in the plasma, as detected bythe first sensor 334, indicates that the interface is close enough tothe low-G wall of the processing chamber to allow all or some of thesecomponents to be swept into the plasma collection line (see FIG. 15B).This condition will also be called an “overspill.”

The second sensor 336 is capable of detecting the hematocrit of the redblood cells in the red blood cell collection tube 294. The decrease ofred blood hematocrit below a set minimum level during processingindicates that the interface is close enough to the high-G wall of theprocessing chamber to allow plasma and/or buffy coat materials to enterthe red blood cell collection tube 294 (see FIG. 15C). This conditionwill also be called an “underspill.”

B. The Sensing Circuit

The sensing station 332 includes a sensing circuit 340 (see FIG. 19), ofwhich the first sensor 334 and second sensor 336 form a part.

The first sensor 334 includes one green light emitting diode (LED) 350,one red LED 352, and two photodiodes 354 and 355. The photodiode 354measures transmitted light and the photodiode 355 measures reflectedlight.

The second sensor 336 includes one red LED 356 and two photodiodes 358and 360. The photodiode 358 measures transmitted light and thephotodiode 360 measures reflected light.

The sensing circuit 340 further includes an LED driver component 342.The driver component 342 includes a constant current source 344, coupledto the LED's 350, 352, and 356 of the sensors 334 and 336. The constantcurrent source 344 supplies a constant current to each LED 350, 352, and356, independent of temperature and the power supply voltage levels. Theconstant current source 344 thereby provides a constant output intensityfor each LED 350, 352, and 356.

The LED drive component 342 includes a modulator 346. The modulator 346modulates the constant current at a prescribed frequency. The modulator346 removes the effects of ambient light and electromagneticinterference (EMI) from the optically sensed reading, as will bedescribed in greater detail later.

The sensing circuit 340 also includes a receiver circuit 348 coupled tothe photodiodes 354, 355, 358, and 360. The receiver circuit 348includes, for each photodiode 354, 355, 358, and 360, a dedicatedcurrent-to-voltage (I-V) converter 362. The remainder of the receivercircuit 348 includes a bandpass filter 364, a programmable amplifier366, and a full wave rectifier 368. These components 364, 366, and 368are shared, e.g., using a multiplexer.

Ambient light typically contains frequency components less than 1000 Hz,and EMI typically contains frequency components above 2 kHz. With thisin mind, the modulator 346 modulates the current at a frequency belowthe EMI frequency components, e.g., at about 2 kHz. The bandpass filter364 has a center frequency of about the same value, i.e., about 2 kHz.The sensing circuit 340 eliminates frequency components above and belowthe ambient light source and EMI components from the sensed measurement.In this way, the sensing circuit 340 is not sensitive to ambientlighting conditions and EMI.

More particularly, transmitted or reflected light from the tube 292 or294 containing the fluid to be measured is incident on photodiodes 354and 355 (for the tube 292) or photodiodes 358 and 360 (for tube 294).Each photodiode produces a photocurrent proportional to the receivedlight intensity. This current is converted to a voltage. The voltage isfed, via the multiplexer 370, to the bandpass filter 364. The bandpassfilter 364 has a center frequency at the carrier frequency of themodulated source light (i.e., 2 kHz in the illustrated embodiment).

The sinusoidal output of the bandpass filter 364 is sent to the variablegain amplifier 366. The gain of the amplifier is preprogrammed inpreestablished steps, e.g., X1, X10, X100, and X1000. This provides theamplifier with the capability to respond to a large dynamic range.

The sinusoidal output of the amplifier 366 is sent to the full waverectifier 368, which transforms the sinusoidal output to a DC outputvoltage proportional to the transmitted light energy.

The controller 16 generates timing pulses for the sensing circuit 340.The timing pulses comprise, for each LED, (i) a modulation square waveat the desired modulation frequency (i.e., 2 kHz in the illustratedembodiment), (ii) an enable signal, (iii) two sensor select bits (whichselect the sensor output to feed to the bandpass filter 364), and (iv)two bits for the receiver circuit gain selection (for the amplifier366).

The controller 16 conditions the driver circuit 342 to operate each LEDin an ON state and an OFF state.

In the ON state, the LED enable is set HIGH, and the LED is illuminatedfor a set time interval, e.g., 100 ms. During the first 83.3 ms of theON state, the finite rise time for the incident photodiode and receivercircuit 348 are allowed to stabilize. During the final 16.7 ms of the ONstate, the output of the circuit 340 is sampled at twice the modulationrate (i.e., 4 kHz in the illustrated embodiment). The sampling intervalis selected to comprise one complete cycle of 60 Hz, allowing the mainfrequency to be filtered from the measurement. The 4 kHz samplingfrequency allows the 2 kHz ripple to be captured for later removal fromthe measurement.

During the OFF state, the LED is left dark for 100 ms. The LED baselinedue to ambient light and electromagnetic interference is recorded duringthe final 16.7 ms.

1. The First Sensor: Platelet/RBC Differentiation

In general, cell free (“free”) plasma has a straw color. As theconcentration of platelets in the plasma increases, the clarity of theplasma decreases. The plasma looks “cloudy.” As the concentration of redblood cells in the plasma increases, the plasma color turns from strawto red.

The sensing circuit 340 includes a detection/differentiation module 372,which analyzes sensed attenuations of light at two different wavelengthsfrom the first sensor 334 (using the transmitted light sensingphotodiode 354). The different wavelengths are selected to possessgenerally the same optical attenuation for platelets, but significantlydifferent optical attenuations for red blood cells.

In the illustrated embodiment, the first sensor 334 includes an emitter350 of light at a first wavelength (λ₁), which, in the illustratedembodiment, is green light (570 nm and 571 nm). The first sensor 334also includes an emitter 352 of light at a second wavelength (λ₂),which, in the illustrated embodiment, is red light (645 nm to 660 nm).

The optical attenuation for platelets at the first wavelength(ε_(platelets) ^(λ) ₁) and the optical attenuation for platelets at thesecond wavelength (ε_(platelets) ^(λ) ₂) are generally the same. Thus,changes in attenuation over time, as affected by increases or decreasesin platelet concentration, will be similar.

However, the optical attenuation for hemoglobin at the first wavelength(ε_(Hb) ^(λ) ₁) is about ten times greater than the optical attenuationfor hemoglobin at the second wavelength (ε_(Hb) ^(λ) ₂). Thus, changesin attenuation over time, as affected by the presence of red bloodcells, will not be similar.

The tube 292, through which plasma is to be sensed, is transparent tolight at the first and second wavelengths. The tube 292 conveys theplasma flow past the first and second emitters 350 and 352.

The light detector 354 receives light emitted by the first and secondemitters 350 and 352 through the tube 292. The detector 354 generatessignals proportional to intensities of received light. The intensitiesvary with optical attenuation caused by the presence of platelets and/orred blood cells.

The module 372 is coupled to the light detector 354 to analyze thesignals to derive intensities of the received light at the first andsecond wavelengths. The module 372 compares changes of the intensitiesof the first and second wavelengths over time. When the intensities ofthe first and second wavelengths change over time in substantially thesame manner, the module 372 generates an output representing presence ofplatelets in the plasma flow. When the intensities of the first andsecond wavelengths change over time in a substantially different manner,the module 372 generates an output representing presence of red bloodcells in the plasma flow. The outputs therefore differentiate betweenchanges in intensity attributable to changes in platelet concentrationin the plasma flow and changes in intensity attributable to changes inred blood cell concentration in the plasma flow.

There are various ways to implement the module 372. In one embodiment,the detection/differentiation module 372 considers that the attenuationof a beam of monochromatic light of wavelength λ by a plasma solutioncan be described by the modified Lambert-Beer law, as follows:I=I _(O) e ^(−[(ε) _(Hb) ^(λC) _(Hb) ^(H+ε) _(platelets) ^(λC)_(platlets) ^()d+G) _(platelets) ^(λ+G) _(RBC) ^(λ])  (1)where:

I is transmitted light intensity.

I_(O) is incident light intensity.

ε_(Hb) ^(λ) is the optical attenuation of hemoglobin (Hb) (gm/dl) at theapplied wavelength.

ε_(platelets) ^(λ) is the optical attenuation of platelets at theapplied wavelength.

C_(Hb) is the concentration of hemoglobin in a red blood cell, taken tobe 34 gm/dl.

C_(platelets) is the concentration of platelets in the sample.

d is the thickness of the plasma stream through the tube 294.

G^(λ) is the path length factor at the applied wavelength, whichaccounts for additional photon path length in the plasma sample due tolight scattering.

H is whole blood hematocrit, which is percentage of red blood cells inthe sample.

G_(RBC) ^(λ) and G_(platelets) ^(λ) are a function of the concentrationand scattering coefficients of, respectively, red blood cells andplatelets at the applied wavelengths, as well as the measurementgeometry.

For wavelengths in the visible and near infrared spectrum, ε_(platelets)^(λ)≈0, therefore:

$\begin{matrix}{{{Ln}\left( \frac{I^{\lambda}}{I_{O}^{\lambda}} \right)} = {{{Ln}\left( T^{\lambda} \right)} \approx {- \left\lbrack {{\left( {ɛ_{Hb}^{\lambda}C_{Hb}H} \right)d} + G_{platelets}^{\lambda} + G_{RBC}^{\lambda}} \right\rbrack}}} & (2)\end{matrix}$

In an overspill condition (shown in FIG. 15B), the first cellularcomponent to be detected by the first sensor 334 in the plasmacollection line 292 will be platelets. Therefore, for the detection ofplatelets, Ln(T^(λ))≈G_(platelets) ^(λ).

To detect the buffy coat interface between the platelet layer and thered blood cell layer, the two wavelengths (λ₁ and λ₂) are chosen basedupon the criteria that (i) λ₁ and λ₂ have approximately the same pathlength factor (G^(λ)), and (ii) one wavelength λ₁ or λ₂ has a muchgreater optical attenuation for hemoglobin than the other wavelength.

Assuming the wavelengths λ₁ and λ₂ have the same G^(λ), Equation (2)reduces to:Ln(T ^(λ) ₁)−Ln(T ^(λ) ₂)≈HdC _(Hb)(ε_(Hb) ^(λ) ₂−ε_(Hb) ^(λ) ₁)   (3)

In one embodiment, λ₁=660 nm (green) and λ₂=571 nm (red). The pathlength factor (G^(λ)) for 571 nm light is greater than for 660 nm light.Therefore the path length factors have to be modified by coefficients αand β, as follows:G_(RBC) ^(λ) ¹ =αG_(RBC) ^(λ) ²G_(platelets) ^(λ) ¹ =βG_(Platelets) ^(λ) ²

Therefore, Equation (3) can be reexpressed as follows:Ln(T ^(λ) ₁)−Ln(T ^(λ) ₂)≈HdC _(Hb)(ε_(Hb) ^(λ) ₂−ε_(Hb) ^(λ) ₁)+(α−1)G_(RBC) ^(λ) ₁+(β−1)G _(platelets) ^(λ) ₂   (4)

In the absence of red blood cells, Equation (3) causes a false red bloodcell detect with increasing platelet concentrations, as Equation (5)demonstrates:Ln(T ^(λ) ₁)−Ln(T ^(λ) ₂)=(β−1)G _(platelets) ^(λ) ₁   (5)

For the detection of platelets and the interface between theplatelet/red blood cell layers, Equation (4) provides a betterresolution. The module 372 therefore applies Equation (4). Thecoefficient (β−1) can be determined by empirically measuringG_(platelets) ^(λ1) and G_(platelets) ^(λ2) in the desired measurementgeometry for different known concentrations of platelets in preparedplatelet-spiked plasma.

The detection/differentiation module 372 also differentiates betweenintensity changes due to the presence of red blood cells in the plasmaor the presence of free hemoglobin in the plasma due to hemolysis. Bothcircumstances will cause a decrease in the output of the transmittedlight sensing photodiode 354. However, the output of the reflected lightsensing photodiode 355 increases in the presence of red blood cells anddecreases in the presence of free hemoglobin. Thedetection/differentiation module 372 thus senses the undesiredoccurrence of hemolysis during blood processing, so that the operatorcan be alerted and corrective action can be taken.

2. The Second Sensor: Packed Red Blood Cell Measurement

In an underspill condition (shown in FIG. 15C), the hematocrit of redblood cells exiting the processing chamber 18 will dramaticallydecrease, e.g., from a targeted hematocrit of about 80 to a hematocritof about 50, as plasma (and the buffy coat) mixes with the red bloodcells. An underspill condition is desirable during a plasma collectionprocedure, as it allows the return of the buffy coat to the donor withthe red blood cells. An underspill condition is not desired during a redblood cell-only collection procedure, as it jeopardizes the yield andquality of red blood cells that are collected for storage.

In either situation, the ability to sense when an underspill conditionexists is desirable.

Photon wavelengths in the near infrared spectrum (NIR) (approximately540 nm to 1000 nm) are suitable for sensing red blood cells, as theirintensity can be measured after transmission through many millimeters ofblood.

The sensing circuit 340 includes a red blood cell detection module 374.The detection module 374 analyzes sensed optical transmissions of thesecond sensor 336 to discern the hematocrit and changes in thehematocrit of red blood cells exiting the processing chamber 18.

The detection module 374 considers that the attenuation of a beam ofmonochromatic light of wavelength λ by blood may be described by themodified Lambert-Beer law, as follows:I=I _(O)e^(−[(ε) _(Hb) ^(λC) _(Hb) ^(H)d+G) _(RBC) ^(λ])  (6)where:

I is transmitted light intensity.

I_(O) is incident light intensity.

ε_(Hb) ^(λ) is the extinction coefficient of hemoglobin (Hb) (gm/dl) atthe applied wavelength.

C_(Hb) is the concentration of hemoglobin in a red blood cell, taken tobe 34 gm/dl.

d is the distance between the light source and light detector.

G^(λ) is the path length factor at the applied wavelength, whichaccounts for additional photon path length in the media due to lightscattering.

H is whole blood hematocrit, which is percentage of red blood cells inthe sample.

G_(RBC) ^(λ) is a function of the hematocrit and scattering coefficientsof red blood cells at the applied wavelengths, as well as themeasurement geometry.

Given Equation (6), the optical density O.D. of the sample can beexpressed as follows:

$\begin{matrix}{{{Ln}\left( \frac{I^{\lambda}}{I_{O}^{\lambda}} \right)} = {{O.D.} \approx {- \left\lbrack {{\left( {ɛ_{Hb}^{\lambda}C_{Hb}H} \right)d} + G_{RBC}^{\lambda}} \right\rbrack}}} & (7)\end{matrix}$

The optical density of the sample can further be expressed as follows:O.D.=O.D. _(Absorption) O.D. _(Scattering)   (8)where:

O.D._(Absorption) is the optical density due to absorption by red bloodcells, expressed as follows:O.D. _(Absorption)=−(ε_(Hb) ^(λ) C _(Hb) H)d   (9)

O.D._(Scattering) is the optical density due to scattering of red bloodcells, expressed as follows:O.D. _(Scattering) =−G _(RBC) ^(λ)  (10)

From Equation (9), O.D._(Absorption) increases linearly with hematocrit(H). For transmittance measurements in the red and NIR spectrum, G_(RBC)^(λ) is generally parabolic, reaching a maximum at a hematocrit ofbetween 50 and 75 (depending on illumination wavelength and measurementgeometry) and is zero at hematocrits of 0 and 100 (see, e.g., Steinke etal., “Diffusion Model of the Optical Absorbance of Whole Blood,” J. Opt.Soc. Am., Vol 5, No. 6, June 1988). Therefore, for light transmissionmeasurements, the measured optical density is a nonlinear function ofhematocrit.

Nevertheless, it has been discovered that G_(RBC) ^(λ) for reflectedlight measured at a predetermined radial distance from the incidentlight source is observed to remain linear for the hematocrit range of atleast 10 to 90. Thus, with the second sensor 336 so configured, thedetection module can treat the optical density of the sample for thereflected light to be a linear function of hematocrit. The samerelationship exists for the first sensor 334 with respect to thedetection of red blood cells in plasma.

This arrangement relies upon maintaining straightforward measurementgeometries. No mirrors or focusing lenses are required. The LED orphotodiode need not be positioned at an exact angle with respect to theblood flow tube. No special optical cuvettes are required. The secondsensor 336 can interface directly with the transparent plastic tubing294. Similarly, the first sensor 334 can interface directly with thetransparent tubing 292.

In the illustrated embodiment, the wavelength 805 nm is selected, as itis an isosbestic wavelength for red blood cells, meaning that lightabsorption by the red blood cells at this wavelength is independent ofoxygen saturation. Still, other wavelengths can be selected within theNIR spectrum.

In the illustrated embodiment, for a wavelength of 805 nm, the setdistance may be 7.5 mm from the light source. The fixture 338, abovedescribed (see FIG. 18), facilitates the placement of the tube 294 inthe desired relation to the light source and the reflected lightdetector of the second sensor 336. The fixture 338 also facilitates theplacement of the tube 292 in the desired relation to the light sourceand the reflected light detector of the first sensor 334.

Measurements at a distance greater than 7.5 mm can be made and will showa greater sensitivity to changes in the red blood cell hematocrit.However a lower signal to noise ratio will be encountered at thesegreater distances. Likewise, measurements at a distance closer to thelight source will show a greater signal to noise ratio, but will be lesssensitive to changes in the red blood cell hematocrit. The optimaldistance for a given wavelength in which a linear relationship betweenhematocrit and sensed intensity exists for a given hematocrit range canbe empirically determined.

The second sensor 336 detects absolute differences in the meantransmitted light intensity of the signal transmitted through the redblood cells in the red blood cell collection line. The detection moduleanalyzes these measured absolute differences in intensities, along withincreases in the standard deviation of the measured intensities, toreliably signal an underspill condition, as FIG. 20 shows.

At a given absolute hematocrit, G_(RBC) ^(λ) varies slightly from donorto donor, due to variations in the mean red blood cell volume and/or therefractive index difference between the plasma and red blood cells.Still, by measuring the reflected light from a sample of a given donor'sblood having a known hematocrit, G_(RBC) ^(λ) may be calibrated toyield, for that donor, an absolute measurement of the hematocrit of redblood cells exiting the processing chamber.

C. Pre-Processing Calibration of the Sensors

The first and second sensors 334 and 336 are calibrated during thesaline and blood prime phases of a given blood collection procedure, thedetails of which have already been described.

During the saline prime stage, saline is conveyed into the bloodprocessing chamber 18 and out through the plasma collection line 292.During this time, the blood processing chamber 18 is rotated in cyclesbetween 0 RPM and 200 RPM, until air is purged from the chamber 18. Thespeed of rotation of the processing chamber 18 is then increased to fulloperational speed.

The blood prime stage follows, during which whole blood is introducedinto the processing chamber 18 at the desired whole blood flow rate(Q_(WB)). The flow rate of plasma from the processing chamber throughthe plasma collection line 292 is set at a fraction (e.g., 80%) of thedesired plasma flow rate (Q_(p)) from the processing chamber 18, topurge saline from the chamber 18. The purge of saline continues underthese conditions until the first sensor 334 optically senses thepresence of saline in the plasma collection line 292.

1. For Plasma Collection Procedures (Induced Underspill)

If the procedure to be performed collects plasma for storage (e.g., thePlasma Collection Procedure or the Red Blood Cell/Plasma CollectionProcedure), an underspill condition is induced during calibration. Theunderspill condition is created by decreasing or stopping the flow ofplasma through the plasma collection line 292. This forces the buffycoat away from the low-G side of the chamber 18 (as FIG. 15C) to assurethat a flow of “clean” plasma exists in the plasma collection line 292,free or essentially free of platelets and leukocytes. The inducedunderspill allows the first sensor 334 to be calibrated and normalizedwith respect to the physiologic color of the donor's plasma, taking intoaccount the donor's background lipid level, but without the presence ofplatelets or leukocytes. The first sensor 334 thereby possesses maximumsensitivity to changes brought about by the presence of platelets orleukocytes in the buffy coat, should an overspill subsequently occurduring processing.

Forcing an underspill condition also positions the interface close tothe high-G wall at the outset of blood processing. This creates aninitial offset condition on the high-G side of the chamber, to prolongthe ultimate development of an overspill condition as blood processingproceeds.

2. Red Blood Cell Collection Procedures

If a procedure is to be performed in which no plasma is to be collected(e.g., the Double Unit Red Blood Cell Collection Procedure), anunderspill condition is not induced during the blood purge phase. Thisis because, in a red blood cell only collection procedure, the firstsensor 334 need only detect, during an overspill, the presence of redblood cells in the plasma. The first sensor 334 does not need to befurther sensitized to detect platelets. Furthermore, in a red blood cellonly collection procedure, it may be desirable to keep the interface asnear the low-G wall as possible. The desired condition allows the buffycoat to be returned to the donor with the plasma and maximizes thehematocrit of the red blood cells collected.

D. Blood Cell Collection 1. Plasma Collection Procedures

In procedures where plasma is collected (e.g., the Plasma CollectionProcedure or the Red Blood Cell/Plasma Collection Procedure), Q_(P) isset at Q_(P(Ideal)), which is an empirically determined plasma flow ratethat allows the system to maintain a steady state collection condition,with no underspills and no overspills.

Q_(P(Ideal)) (in grams/ml) is a function of the anticoagulated wholeblood inlet flow rate Q_(WB), the anticoagulant whole blood inlethematocrit HCT_(WB), and the red blood cell exit hematocrit HCT_(RBC)(as estimated or measured), expressed as follows:

$Q_{P{({Ideal})}} = \left( {\rho_{Plasma}Q_{WB}*\frac{\left( {1 - {H\; C\; T_{WB}}} \right) - \left\lbrack {\frac{\rho_{WB}}{\rho_{RBC}}\left( {1 - {H\; C\; T_{RBC}}} \right)} \right\rbrack}{\left( {1 - \frac{\rho_{plasma}}{\rho_{RBC}}} \right)\left( {1 - {H\; C\; T_{RBC}}} \right)}} \right.$where:

ρ_(Plasma) is the density of plasma (in g/ml)=1.03

ρ_(WB) is the density of whole blood (in g/ml)=1.05

ρ_(RBC) is the density of red blood cells=1.08

Q_(WB) is set to the desired whole blood inlet flow rate for plasmacollection, which, for a plasma only collection procedure, is generallyabout 70 ml/min. For a red blood cell/plasma collection procedure,Q_(WB) is set at about 50 ml/min, thereby providing packed red bloodcells with a higher hematocrit than in a traditional plasma collectionprocedure.

The system controller 16 maintains the pump settings until the desiredplasma collection volume is achieved, unless an underspill condition oran overspill condition is detected.

If set Q_(P) is too high for the actual blood separation conditions, or,if due to the physiology of the donor, the buffy coat volume is larger(i.e., “thicker”) than expected, the first sensor 334 will detect thepresence of platelets or leukocytes, or both in the plasma, indicatingan overspill condition.

In response to an overspill condition caused by a high Q_(P), the systemcontroller 16 terminates operation of the plasma collection pump PP2,while keeping set Q_(WB) unchanged. In response to an overspillcondition caused by a high volume buffy coat, the system controller 16terminates operation of the plasma collection pump PP2, until anunderspill condition is detected by the red blood cell sensor 336. Thisserves to expel the buffy coat layer from the separation chamber throughthe red blood cell tube 294.

To carry out the overspill response, the blood processing circuit 46 isprogrammed to operate the in-process pump PP1 (i.e., drawing in throughthe valve V9 and expelling out of the valve V14), to draw whole bloodfrom the in-process container 312 into the processing chamber 18 at theset Q_(WB). Red blood cells exit the chamber 18 through the tube 294 forcollection in the collection container 308. The flow rate of red bloodcells directly depends upon the magnitude of Q_(WB).

During this time, the blood processing circuit 46 is also programmed tocease operation of the plasma pump PP2 for a preestablished time period(e.g., 20 seconds). This forces the interface back toward the middle ofthe separation chamber. After the preestablished time period, theoperation of the plasma pump PP2 is resumed, but at a low flow rate(e.g., 10 ml/min) for a short time period (e.g., 10 seconds). If thespill has been corrected, clean plasma will be detected by the firstsensor 334, and normal operation of the blood processing circuit 46 isresumed. If clean plasma is not sensed, indicating that the overspillhas not been corrected, the blood processing circuit 46 repeats theabove-described sequence.

The programming of the circuit to relieve an overspill condition issummarized in the following table.

TABLE Programming of Blood Processing Circuit To Relieve An OverspillCondition (Plasma Collection Procedures) V1 ● V2 ◯ V3 ● V4 ● V5 ◯ V6 ●V7 ● V8 ● V9 ◯/● Pump In V10 ● V11 ● V12 ● V13 ● V14 ◯/● Pump Out V15 ●V16 ● V17 ● V18 ● V19 ● V20 ● V21 ● V22 ● V23 ● PP1 □ PP2 ▪ PP3 ▪ PP4 ▪Caption: ◯ denotes an open valve; ● denotes a closed valve; ◯/● denotesa valve opening and closing during a pumping sequence; ▪ denotes an idlepump station (not in use); and □ denotes a pump station in use.

Upon correction of an overspill condition, the controller 16 returns theblood processing circuit 46 to resume normal blood processing, butapplies a percent reduction factor (%RF) to the Q_(P) set at the timethe overspill condition was initially sensed. The reduction factor (%RF)is a function of the time between overspills, i.e., %RF increases as thefrequency of overspills increases, and vice versa.

If set Q_(P) is too low, the second sensor 336 will detect a decrease inthe red blood cell hematocrit below a set level, which indicates anunderspill condition.

In response to an underspill condition, the system controller 16 resetsQ_(P) close to the set Q_(WB). As processing continues, the interfacewill, in time, move back toward the low-G wall. The controller 16maintains these settings until the second sensor 336 detects a red bloodcell hematocrit above the desired set level. At this time, thecontroller 16 applies a percent enlargement factor (%EF) to the Q_(P)set at the time the underspill condition was initially sensed. Theenlargement factor (%EF) is a function of the time between underspills,i.e., %EF increases as the frequency of underspills increases.

Should the controller 16 be unable to correct a given under- oroverspill condition after multiple attempts (e.g., three attempts), analarm is commanded.

2. Red Blood Cell Only Collection Procedures

In procedures where only red blood cells and no plasma is collected(e.g., the Double Unit Red Blood Cell Collection Procedure), Q_(P) isset to no greater than Q_(P(Ideal)), and Q_(WB) is set to the desiredwhole blood inlet flow rate into the processing chamber 18 for theprocedure, which is generally about 50 ml/min for a double unit redblood cell collection procedure.

It may be desired during a double unit red blood cell collectionprocedure that overspills occur frequently. This maximizes thehematocrit of the red blood cells for collection and returns the buffycoat to the donor with the plasma. Q_(P) is increased over time ifoverspills occur at less than a set frequency. Likewise, Q_(P) isdecreased over time if overspills occur above the set frequency.However, to avoid an undesirably high hematocrit, it may be just asdesirable to operate at Q_(P(Ideal)).

The system controller 16 controls the pump settings in this way untilthe desired red blood cell collection volume is achieved, taking care ofunderspills or overspills as they occur.

The first sensor 334 detects an overspill by the presence of red bloodcells in the plasma. In response to an overspill condition, the systemcontroller 16 terminates operation of the plasma collection pump to drawplasma from the processing chamber, while keeping the set Q_(WB)unchanged.

To implement the overspill response, the blood processing circuit 46 isprogrammed (through the selective application of pressure to the valvesand pump stations) to operate the plasma pump PP2 and in-process pumpPP1 in the manner set forth in the immediately preceding Table. The redblood cells detected in the tube 292 are thereby returned to theprocessing chamber 18, and are thereby prevented from entering theplasma collection container 304.

The interface will, in time, move back toward the high-G wall. Thecontroller 16 maintains these settings until the second sensor 336detects a decrease in the red blood cell hematocrit below a set level,which indicates an underspill condition.

In response to an underspill condition, the system controller 16increases Q_(P) until the second sensor 336 detects a red blood cellhematocrit above the desired set level. At this time, the controller 16resets Q_(P) to the value at the time the most recent overspillcondition was sensed.

3. Buffy Coat Collection

If desired, an overspill condition can be periodically induced during agiven plasma collection procedure to collect the buffy coat in a buffycoat collection container 376 (see FIG. 10). As FIG. 10 shows, in theillustrated embodiment, the buffy coat collection container 376 iscoupled by tubing 378 to the buffy port P4 of the cassette 28. The buffycoat collection container 376 is suspended on a weigh scale 246, whichprovides output reflecting weight changes over time, from which thecontroller 16 derives the volume of buffy coat collected.

In this arrangement, when the induced overspill condition is detected,the blood processing circuit 46 is programmed (through the selectiveapplication of pressure to the valves and pump stations) to operate theplasma pump PP2 (i.e., drawing in through valve V12 and expelling outthrough valve V10), to draw plasma from the processing chamber 18through the tube 378, while valves V4 and V6 are closed and valve V8 isopened. The buffy coat in the tube 378 is conveyed into the buffy coatcollection container 376. The blood processing circuit 46 is alsoprogrammed during this time to operate the in-process pump PP1 (i.e.,drawing in through the valve V9 and expelling out of the valve V14), todraw whole blood from the in-process container 312 into the processingchamber 18 at the set Q_(WB). Red blood cells exit the chamber 18through the tube 294 for collection in the collection container 308.

The programming of the circuit to relieve an overspill condition bycollecting the buffy coat in the buffy coat collection container 376 issummarized in the following table.

TABLE Programming of Blood Processing Circuit To Relieve An OverspillCondition by Collecting the Buffy Coat (Plasma Collection Procedures) V1● V2 ● V3 ● V4 ● V5 ● V6 ● V7 ● V8 ◯ V9 ◯/● Pump In V10 ◯/● Pump Out V11● V12 ◯/● Pump In V13 ● V14 ◯/● Pump Out V15 ● V16 ● V17 ● V18 ● V19 ●V20 ● V21 ● V22 ● V23 ● PP1 □ PP2 □ PP3 ▪ PP4 ▪ Caption: ◯ denotes anopen valve; ● denotes a closed valve; ◯/● denotes a valve opening andclosing during a pumping sequence; ▪ denotes an idle pump station (notin use); and □ denotes a pump station in use.

After a prescribed volume of buffy coat is conveyed into the buffy coatcollection container 376 (as monitored by the weigh scale 246), normalblood processing conditions are resumed. Overspill conditions causingthe movement of the buffy coat into the tube 378 can be induced atprescribed intervals during the process period, until a desired buffycoat volume is collected in the buffy coat collection container.

VI. Another Programmable Blood Processing Circuit A. Circuit Schematic

As previously mentioned, various configurations for the programmableblood processing circuit 46 are possible. FIG. 5 schematically shows onerepresentative configuration 46, the programmable features of which havebeen described. FIG. 34 shows another representative configuration of ablood processing circuit 46′ having comparable programmable features.

Like the circuit 46, the circuit 46′ includes several pump stationsPP(N), which are interconnected by a pattern of fluid flow paths F(N)through an array of in-line valves V(N). The circuit is coupled to theremainder of the blood processing set by ports P(N).

The circuit 46′ includes a programmable network of flow paths F1 to F33.The circuit 46′ includes eleven universal ports P1 to P8 and P11 to P13and four universal pump stations PP1, PP2, PP3, and PP4. By selectiveoperation of the in-line valves V1 to V21 and V23 to V25, any universalport P1 to P8 and P11 to P13 can be placed in flow communication withany universal pump station PP1, PP2, PP3, and PP4. By selectiveoperation of the universal valves, fluid flow can be directed throughany universal pump station in a forward direction or reverse directionbetween two valves, or an in-out direction through a single valve.

In the illustrated embodiment, the circuit 46′ also includes an isolatedflow path (comprising flow paths F9, F23, F24, and F10) with two portsP9 and P10 and one in-line pump station PP5. The flow path is termed“isolated,” because it cannot be placed into direct flow communicationwith any other flow path in the circuit 46′ without exterior tubing. Byselective operation of the in-line valves V21 and V22, fluid flow can bedirected through the pump station PP5 in a forward direction or reversedirection between two valves, or an in-out direction through a singlevalve.

Like circuit 46, the circuit 46′ can be programmed to assign dedicatedpumping functions to the various pump stations. In one embodiment, theuniversal pump stations PP3 and PP4 in tandem serve as a generalpurpose, donor interface pump, regardless of the particular bloodprocedure performed. The dual donor interface pump stations PP3 and PP4in the circuit 46′ work in parallel. One pump station draws fluid intoits pump chamber, while the other pump station expels fluid from itspump chamber. The pump station PP3 and PP4 alternate draw and expelfunctions.

In one arrangement, the draw cycle for the drawing pump station is timedto be longer than the expel cycle for the expelling pump station. Thisprovides a continuous flow of fluid on the inlet side of the pumpstations and a pulsatile flow in the outlet side of the pump stations.In one representative embodiment, the draw cycle is ten seconds, and theexpel cycle is one second. The expelling pump station performs its onesecond cycle at the beginning of the draw cycle of the drawing pump, andthen rests for the remaining nine seconds of the draw cycle. The pumpstations then switch draw and expel functions. This creates a continuousinlet flow and a pulsatile outlet flow. The provision of two alternatingpump stations PP3 and PP4 serves to reduce overall processing time, asfluid is continuously conducted into a drawing pump station throughoutthe procedure.

In this arrangement, the isolated pump station PP5 of the circuit 46′serves as a dedicated anticoagulant pump, like pump station PP4 in thecircuit 46, to draw anticoagulant from a source through the port P10 andto meter anticoagulant into the blood through port P9.

In this arrangement, as in the circuit 46, the universal pump stationPP1 serves, regardless of the particular blood processing procedureperformed, as a dedicated in-process whole blood pump, to convey wholeblood into the blood separator. As in the circuit 46, the dedicatedfunction of the pump station PP1 frees the donor interface pumps PP3 andPP4 from the added function of supplying whole blood to the bloodseparator. Thus, the in-process whole blood pump PP1 can maintain acontinuous supply of blood to the blood separator, while the donorinterface pumps PP3 and PP4 operate in tandem to simultaneously draw andreturn blood to the donor through the single phlebotomy needle. Thecircuit 46′ thus minimizes processing time.

In this arrangement, as in circuit 46, the universal pump station PP2 ofthe circuit 46′ serves, regardless of the particular blood processingprocedure performed, as a plasma pump, to convey plasma from the bloodseparator. As in the circuit 46, the ability to dedicate separatepumping functions in the circuit 46′ provides a continuous flow of bloodinto and out of the separator, as well as to and from the donor.

The circuit 46′ can be programmed to perform all the differentprocedures described above for the circuit 46. Depending upon theobjectives of the particular blood processing procedure, the circuit 46′can be programmed to retain all or some of the plasma for storage orfractionation purposes, or to return all or some of the plasma to thedonor. The circuit 46′ can be further programmed, depending upon theobjectives of the particular blood processing procedure, to retain allor some of the red blood cells for storage, or to return all or some ofthe red blood cells to the donor. The circuit 46′ can also beprogrammed, depending upon the objectives of the particular bloodprocessing procedure, to retain all or some of the buffy coat forstorage, or to return all or some of the buffy coat to the donor.

In the embodiment illustrated in FIG. 34, the circuit 46′ forms a partof a universal set 264′, which is coupled to the ports P1 to P13.

More particularly, a donor tube 266′, with attached phlebotomy needle268′ is coupled to the port P8 of the circuit 46′. An anticoagulant tube270′, coupled to the phlebotomy needle 268′ is coupled to port P9. Acontainer 276′ holding anticoagulant is coupled via a tube 274′ to theport P10.

A container 280′ holding a red blood cell additive solution is coupledvia a tube 278′ to the port P11. A container 288′ holding saline iscoupled via a tube 284′ to the port P12. A storage container 289′ iscoupled via a tube 291′ to the port P13. An in-line leukocyte depletionfilter 293′ is carried by the tube 291′ between the port P13 and thestorage container 289′. The containers 276′, 280′, 288′, and 289′ can beintegrally attached to the ports or can be attached at the time of usethrough a suitable sterile connection, to thereby maintain a sterile,closed blood processing environment.

Tubes 290′, 292′, and 294′ extend to an umbilicus 296′ which is coupledto the processing chamber 18′. The tubes 290′, 292′, and 294 arecoupled, respectively, to the ports P5, P6, and P7. The tube 290′conveys whole blood into the processing chamber 18 under the operationof the in-process pump station PP1. The tube 292′ conveys plasma fromthe processing chamber 18′ under the operation of the plasma pumpstation PP2. The tube 294′ conveys red blood cells from processingchamber 18′.

A plasma collection container 304′ is coupled by a tube 302′ to the portP3. The collection container 304′ is intended, in use, to serve as areservoir for plasma during processing.

A red blood cell collection container 308′ is coupled by a tube 306′ tothe port P2. The collection container 308′ is intended, in use, toreceive a unit of red blood cells for storage.

A buffy coat collection container 376′ is coupled by a tube 377′ to theport P4. The container 376′ is intended, in use, to receive a volume ofbuffy coat for storage.

A whole blood reservoir 312′ is coupled by a tube 310′ to the port P1.The collection container 312′ is intended, in use, to receive wholeblood during operation of the donor interface pumps PP3 and PP4, toserve as a reservoir for whole blood during processing. It can alsoserve to receive a second unit of red blood cells for storage.

B. The Cassette

As FIGS. 35 and 36 show, the programmable fluid circuit 46′ can beimplemented as an injection molded, pneumatically controlled cassette28′. The cassette 28′ interacts with the pneumatic pump and valvestation 30, as previously described, to provide the same centralized,programmable, integrated platform as the cassette 28.

FIGS. 35 and 36 show the cassette 28′ in which the fluid circuit 46′(schematically shown in FIG. 34) is implemented. As previously describedfor the cassette 28, an array of interior wells, cavities, and channelsare formed on both the front and back sides 190′ and 192′ of thecassette body 188′, to define the pump stations PP1 to PP5, valvestations V1 to V25, and flow paths F1 to F33 shown schematically in FIG.34. In FIG. 36, the flow paths F1 to F33 are shaded to facilitate theirviewing. Flexible diaphragms 194′ and 196′ overlay the front and backsides 190′ and 192′ of the cassette body 188′, resting against theupstanding peripheral edges surrounding the pump stations PP1 to PP5,valves V1 to V25, and flow paths F1 to F33. The pre-molded ports P1 toP13 extend out along two side edges of the cassette body 188′.

The cassette 28′ is vertically mounted for use in the pump and valvestation 30 in the same fashion shown in FIG. 2. In this orientation(which FIG. 36 shows), the side 192′ faces outward, ports P8 to P13 facedownward, and the ports P1 to P7 are vertically stacked one above theother and face inward.

As previously described, localized application by the pump and valvestation 30 of positive and negative fluid pressures upon the diaphragm194′ serves to flex the diaphragm to close and open the valve stationsV1 to V25 or to expel and draw liquid out of the pump stations PP1 toPP5.

An additional interior cavity 200′ is provided in the back side 192′ ofthe cassette body 188′. The cavity 200′ forms a station that holds ablood filter material to remove clots and cellular aggregations that canform during blood processing. As shown schematically in FIG. 34, thecavity 200′ is placed in the circuit 46′ between the port P8 and thedonor interface pump stations PP3 and PP4, so that blood returned to thedonor passes through the filter. Return blood flow enters the cavity200′ through flow path F27 and exits the cavity 200′ through flow pathF8. The cavity 200′ also serves to trap air in the flow path to and fromthe donor.

Another interior cavity 201′ (see FIG. 35) is also provided in the backside 192′ of the cassette body 188′. The cavity 201′ is placed in thecircuit 46′ between the port P5 and the valve V16 of the in-processpumping station PP1. Blood enters the cavity 201′ from flow path F16through opening 203′ and exits the cavity 201′ into flow path F5 throughopening 205′. The cavity 201′ serves as another air trap within thecassette body 188′ in the flow path serving the separation chamber 18′.The cavity 201′ also serves as a capacitor to dampen the pulsatile pumpstrokes of the in-process pump PP1 serving the separation chamber.

C. Associated Pneumatic Manifold Assembly

FIG. 43 shows a pneumatic manifold assembly 226′ that can be used inassociation with the cassette 28′, to supply positive and negativepneumatic pressures to convey fluid through the cassette 28′. The frontside 194′ of the diaphragm is held in intimate engagement against themanifold assembly 226′ when the door 32 of the centrifuge station 20 isclosed and the bladder 314 inflated. The manifold assembly 226′, underthe control of the controller 16, selectively distributes the differentpressure and vacuum levels to the pump and valve actuators PA(N) andVA(N) of the cassette 28′. These levels of pressure and vacuum aresystematically applied to the cassette 28′, to route blood andprocessing liquids. Under the control of a controller 16, the manifoldassembly 226′ also distributes pressure levels to the door bladder 314(already described), as well as to a donor pressure cuff (also alreadydescribed) and to a donor line occluder 320 (also already described).The manifold assembly 226′ for the cassette 28′ shown in FIG. 43 sharesmany attributes with the manifold assembly 226 previously described forthe cassette 28, as shown in FIG. 12.

Like the manifold assembly 226, the manifold assembly 226′ is coupled toa pneumatic pressure source 234′, which is carried inside the lid 40behind the manifold assembly 226′. As in the manifold assembly 226, thepressure source 234′ for the manifold assembly 226′ comprises twocompressors C1′ and C2′, although one or several dual-head compressorscould be used as well. Compressor C1′ supplies negative pressure throughthe manifold 226′ to the cassette 28′. The other compressor C2′ suppliespositive pressure through the manifold 226′ to the cassette 28′.

As FIG. 43 shows, the manifold 226′ contains five pump actuators PA1 toPA5 and twenty-five valve actuators VA1 to VA25. The pump actuators PA1to PA5 and the valve actuators VA1 to VA25 are mutually oriented to forma mirror image of the pump stations PP1 to PP5 and valve stations V1 toV25 on the front side 190′ of the cassette 28′.

Like the manifold assembly 226, the manifold assembly 226′ shown in FIG.43 includes an array of solenoid actuated pneumatic valves, which arecoupled in-line with the pump and valve actuators PA1 to PA5 and VA1 toVA25.

Like the manifold assembly 226, the manifold assembly 226′ maintainsseveral different pressure and vacuum conditions, under the control ofthe controller 16.

As previously described in connection with the manifold assembly 226,Phard, or Hard Pressure, and Pinpr, or In-Process Pressure are highpositive pressures (e.g., +500 mmHg) maintained by the manifold assembly226′ for closing the cassette valves V1 to V25 and to drive theexpression of liquid from the in-process pump PP1 and the plasma pumpPP2. As before explained, the magnitude of Pinpr must be sufficient toovercome a minimum pressure of approximately 300 mmHg, which istypically present within the processing chamber 18′. Pinpr and Phard areoperated at the highest pressure to ensure that upstream and downstreamvalves used in conjunction with pumping are not forced open by thepressures applied to operate the pumps.

Pgen, or General Pressure (+300 mmHg), is applied to drive theexpression of liquid from the donor interface pumps PP3 and PP4 and theanticoagulant pump PP5.

Vhard, or Hard Vacuum (−350 mmHg), is the deepest vacuum applied in themanifold assembly 226′ to open cassette valves V1 to V25. Vgen, orGeneral Vacuum (−300 mmHg), is applied to drive the draw function ofeach of the pumps PP1 to PP5. Vgen is required to be less extreme thanVhard, to ensure that pumps PP1 to PP5 do not overwhelm upstream anddownstream cassette valves V1 to V25.

A main hard pressure line 322′ and a main vacuum line 324′ distributePhard and Vhard in the manifold assembly 226′. The pressure and vacuumsources 234′ run continuously to supply Phard to the hard pressure line322′ and Vhard to the hard vacuum line 324′. A pressure sensor S2monitors Phard in the hard pressure line 322′. The sensor S2 opens andcloses the solenois SO32 to build Phard up to its maximum set value.

Similarly, a pressure sensor S8 in the hard vacuum line 324′ monitorsVhard. The sensor S8 controls a solenois SO43 to maintain Vhard as itsmaximum value.

A general pressure line 326′ branches from the hard pressure line 322′.A sensor S4 in the general pressure line 326′ monitors Pgen. The sensorS4 controls a solenois SO34 to maintain Pgen within its specifiedpressure range.

A general vacuum line 330′ branches from the hard vacuum line 324′. Asensor S5 monitors Vgen in the general vacuum line 330′. The sensor S5controls a solenois SO45 to keep Vgen within its specified vacuum range.

In-line reservoirs R1 to R4 are provided in the hard pressure line 322′,the general pressure line 326′, the hard vacuum line 324′, and thegeneral vacuum line 330′. The reservoirs R1 to R4 assure that theconstant pressure and vacuum adjustments as above described are smoothand predictable.

The solenoids SO32 and SO43 provide a vent for the pressures andvacuums, respectively, upon procedure completion.

The solenoids SO41, SO42, SO47, and SO48 provide the capability toisolate the reservoirs R1 to R4 from the air lines that supply vacuumand pressure to the pump and valve actuators. This provides for muchquicker pressure/vacuum decay feedback, so that testing ofcassette/manifold assembly seal integrity can be accomplished.

The solenoids SO1 to SO25 provide Phard or Vhard to drive the valveactuators VA1 to V25. The solenoids SO27 and SO28 provide Pinpr and Vgento drive the in-process and plasma pumps PP1 and PP2. The solenoids SO30and SO31 provide Pgen and Vgen to drive the donor interface pumps PP3and PP4. The solenois SO29 provides Pgen and Vgen to drive the AC pumpPP5.

The solenois SO35 provides isolation of the door bladder 314 from thehard pressure line 322′ during the procedure. A sensor S1 monitors Pdoorand control the solenois SO35 to keep the pressure within its specifiedrange.

The solenois SO40 provides Phard to open the safety occluder valve 320.Any error modes that might endanger the donor will relax (vent) thesolenoid SO40 to close the occluder 320 and isolate the donor.Similarly, any loss of power will relax the solenois SO40 and isolatethe donor.

The sensor S3 monitors Pcuff and communicates with solenois SO36 (forincreases in pressure) and solenois SO37 (for venting) to maintain thedonor cuff within its specified ranges during the procedure.

As before explained, any solenoid can be operated in “normally open”mode or can be re-routed pneumatically to be operated in a “normallyclosed” mode, and vice versa.

D. Exemplary Pumping Functions

Based upon the foregoing description of the programming of the fluidcircuit 46 implemented by the cassette 28, one can likewise program thefluid circuit 46′ implemented by the cassette 28′ to perform all thevarious blood process functions already described. Certain pumpingfunctions for the fluid circuit 46′, common to various blood processingprocedures, will be described by way of example.

1. Whole Blood Flow to the In-Process Container

In a first phase of a given blood collection cycle, the blood processingcircuit 46′ is programmed (through the selective application of pressureto the valves and pump stations of the cassette 28′) to jointly operatethe donor interface pumps PP3 and PP4 to transfer anticoagulated wholeblood into the in-process container 312′ prior to separation.

In a first phase (see FIG. 37A), the pump PP3 is operated in a tensecond draw cycle (i.e., in through valves V12 and V13, with valves V6,V14, V18, and V15 closed) in tandem with the anticoagulant pump PP5(i.e., in through valve V22 and out through valve V21) to drawanticoagulated blood through the donor tube 270′ into the pump PP3. Atthe same time, the donor interface pump PP4 is operated in a one secondexpel cycle to expel (out through valve V7) anticoagulated blood fromits chamber into the in-process container 312′ through flow paths F20and F1 (through opened valve V4).

At the end of the draw cycle for pump PP3 (see FIG. 37B), the bloodprocessing circuit 46′ is programmed to operate the donor interface pumpPP4 in a ten second draw cycle (i.e., in through valves V12 and V14,with valves V13 and V18 closed) in tandem with the anticoagulant pumpPP5 to draw anticoagulated blood through the donor tube 270′ into thepump PP4. At the same time, the donor interface pump PP3 is operated ina one second expel cycle to expel (out through valve V6) anticoagulatedblood from its chamber into the in-process container 312′ through theflow paths F20 and F1 (through opened valve V4).

These alternating cycles continue until an incremental volume ofanticoagulated whole blood enters the in-process container 312′, asmonitored by a weigh sensor. As FIG. 37C shows, the blood processingcircuit 46′ is programmed to operate the in-process pump station PP1(i.e., in through valve V1 and out through valve V16) and the plasmapump PP2 (i.e., in through valve V17 and out through valve V11, withvalve V9 opened and valve V10 closed) to convey anticoagulated wholeblood from the in-process container 312′ into the processing chamber 18′for separation, while removing plasma into the plasma container 304′(through opened valve V9) and red blood cells into the red blood cellcontainer 308′ (through open valve V2), in the manner previouslydescribed with respect to the circuit 46. This phase continues until anincremental volume of plasma is collected in the plasma collectioncontainer 304′ (as monitored by the weigh sensor) or until a targetedvolume of red blood cells is collected in the red blood cell collectioncontainer (as monitored by the weigh sensor). The donor interface pumpsPP3 and PP4 toggle to perform alternating draw and expel cycles asnecessary to keep the volume of anticoagulated whole blood in thein-process container 312′ between prescribed minimum and maximum levels,as blood processing proceeds.

2. Red Blood Cell Return with In-Line Addition of Saline

When it is desired to return red blood cells to the donor (see FIG.37D), the blood processing circuit 46′ is programmed to operate thedonor interface pump station PP3 in a ten second draw cycle (i.e., inthrough valve V6, with valves V13 and V7 closed) to draw red blood cellsfrom the red blood cell container 308′ into the pump PP3 (through openvalves V2, V3, and V5, valve V10 being closed). At the same time, thedonor interface pump PP4 is operated in a one second expel cycle toexpel (out through valves V14 and V18, with valves V12 and V21 closed)red blood cells from its chamber to the donor through the filter cavity200′.

At the end of the draw cycle for pump PP3 (see FIG. 37E), the bloodprocessing circuit 46′ is programmed to operate the donor interface pumpPP4 in ten second draw cycle (i.e., in through valve V7, with valves V6and V14 closed) to draw red blood cells from the red blood cellcontainer 308′ into the pump PP4. At the same time, the donor interfacepump PP3 is operated in a one second expel cycle to expel (out throughvalves V13 and V18, with valve V12 closed) red blood cells from itschamber to the donor through the filter chamber 200′. These alternatingcycles continue until a desired volume of red blood cells is returned tothe donor.

Simultaneously, valves V24, V20, and V8 are opened, so that the drawingpump station PP3 or PP4 also draws saline from the saline container 288′for mixing with red blood cells drawn into the chamber. As beforeexplained, the in-line mixing of saline with the red blood cells raisesthe saline temperature and improves donor comfort, while also loweringthe hematocrit of the red blood cells.

Simultaneously, the in-process pump PP1 is operated (i.e., in throughvalve V1 and out through valve V16) and the plasma pump PP2 (i.e., inthrough valve V17 and out through valve V11, with valve V9 open) toconvey anticoagulated whole blood from the in-process container 312′into the processing chamber for separation, while removing plasma intothe plasma container 304′, in the manner previously described withrespect to the fluid circuit 46.

3. In-Line Addition of Red Blood Cell Additive Solution

In a blood processing procedure where red blood cells are collected forstorage (e.g., the Double Red Blood Cell Collection Procedure or the RedBlood Cell and Plasma Collection Procedure) the circuit 46′ isprogrammed to operate the donor interface pump station PP3 in a tensecond draw cycle (in through valves V15 and V13, with valve V23 openedand valves V8, V12 and V18 closed) to draw red blood cell storagesolution from the container 280′ into the pump PP3 (see FIG. 38A).Simultaneously, the circuit 46′ is programmed to operate the donorinterface pump station PP4 in a one second expel cycle (out throughvalve V7, with valves V14 and V18 closed) to expel red blood cellstorage solution to the container(s) where red blood cells reside (e.g.,the in-process container 312′ (through open valve V4) or the red bloodcell collection container 308′ (through open valves V5, V3, and V2, withvalve V10 closed)).

At the end of the draw cycle for pump PP3 (see FIG. 38B), the bloodprocessing circuit 46′ is programmed to operate the donor interface pumpPP4 in a ten second draw cycle (i.e., in through valve V14, with valvesV7, V18, V12, and V13 closed) to draw red blood cell storage solutionfrom the container 280′ into the pump PP4. At the same time, the donorinterface pump PP3 is operated in a one second expel cycle to expel (outthrough valve V6, with valves V13 and V12 closed) red blood cell storagesolution to the container(s) where red blood cells reside. Thesealternating cycles continue until a desired volume of red blood cellstorage solution is added to the red blood cells.

4. In-Line Leukocyte Depletion

Circuit 46′ provides the capability to conduct on-line depletion ofleukocytes from collected red blood cells. In this mode (see FIG. 39A),the circuit 46′ is programmed to operate the donor interface pumpstation PP3 in a ten second draw cycle (in through valve V6, with valvesV13 and V12 closed) to draw red blood cells from the container(s) wherered blood cells reside (e.g., the in-process container 312′ (throughopen valve V4) or the red blood cell collection container 308′ (throughopen valves V5, V3, and V2, with valve V10 closed)) into the pump PP3.Simultaneously, the circuit 46′ is programmed to operate the donorinterface pump station PP4 in a one second expel cycle (out throughvalve V14, with valves V18 and V8 closed and valves V15 and V25 opened)to expel red blood cells through tube 291′ through the in-line leukocytedepletion filter 293′ to the leukocyte-depleted red blood cell storagecontainer 289′.

At the end of the draw cycle for pump PP3 (see FIG. 39B), the bloodprocessing circuit 46′ is programmed to operate the donor interface pumpPP4 in a ten second draw cycle (i.e., in through valve V7, with valvesV14 and V18 closed) to draw red blood cells from the container 312′ or308′ into the pump PP4. At the same time, the donor interface pump PP3is operated in a one second expel cycle to expel (out through valve V13,with valve V12 closed and valves V15 and V25 opened) red blood cellsthrough tube 291′ through the in-line leukocyte depletion filter 293′ tothe leukocyte-depleted red blood cell storage container 289′. Thesealternating cycles continue until a desired volume of red blood cells istransferred through the filter 293′ into the container 289′.

5. Staged Buffy Coat Harvesting

In circuit 46 (see FIG. 5), buffy coat is collected through port P4,which is served by flow line F4, which branches from flow line F28,which conveys plasma from the plasma pump station PP2 to the plasmacollection container 304 (also see FIG. 10). In the circuit 46′ (seeFIG. 34), the buffy coat is collected through the port P4 from the flowpath F6 as controlled by valve V19. The buffy coat collection pathbypasses the plasma pump station PP2, keeping the plasma pump stationPP2 free of exposure to the buffy coat, thereby keeping the collectedplasma free of contamination by the buffy coat components.

During separation, the system controller (already described) maintainsthe buffy coat layer within the separation chamber 18′ at a distancespaced from the low-G wall, away from the plasma collection line 292(see FIG. 15A). This allows the buffy coat component to accumulateduring processing as plasma is conveyed by operation of the plasma pumpPP2 from the chamber into the plasma collection container 304′.

To collect the accumulated buffy coat component, the controller opensthe buffy coat collection valve V19, and closes the inlet valve V17 ofthe plasma pump station PP2 and the red blood cell collection valve V2.The in-process pump PP1 continues to operate, bringing whole blood intothe chamber 18′. The flow of whole blood into the chamber 18′ moves thebuffy coat to the low-G wall, inducing an overspill condition (see FIG.15B). The buffy coat component enters the plasma collection line 292′and enters flow path F6 through the port P6. The circuit 46′ conveys thebuffy coat component in F6 through the opened valve V19 directly intopath F4 for passage through the port P4 into the collection container376′.

The valve V19 is closed when the sensing station 332 senses the presenceof red blood cells. The plasma pumping station PP2 can be temporarilyoperated in a reverse flow direction (in through the valve V11 and outthrough the valve V17, with valve V9 opened) to flow plasma from thecollection container 304′ through the tube 292′ toward the separationchamber, to flush resident red blood from the tube 292′ back into theseparation chamber. The controller can resume normal plasma and redblood cell collection, by opening the red blood cell collection valve V2and operating the plasma pumping station PP2 (in through valve V17 andout through valve V11) to resume the conveyance of plasma from theseparation chamber to the collection container 304′.

Overspill conditions causing the movement of the buffy coat forcollection can be induced at prescribed intervals during the processperiod, until a desired buffy coat volume is collected in the buffy coatcollection container.

6. Miscellaneous

As FIG. 43 shows in phantom lines, the manifold assembly 226′ caninclude an auxiliary pneumatic actuator A_(AUX) to selectively applyP_(HARD) to the region of the flexible diaphragm that overlies theinterior cavity 201′ (see FIG. 35). As previously described, whole bloodexpelled by the pumping station PP1 (by application of P_(HARD) byactuator PA1), enters flow path F5 through openings 203′ and 205′ intothe processing chamber 18′. During the next subsequent stroke of thepumping station PP1, to draw whole blood into the pumping station PP1 byapplication of V_(GEN) by actuator PA1, residual whole blood residing inthe cavity 201′ is expelled into flow path F5 through opening 205′, andinto the processing chamber 18′ by application of P_(HARD) by A_(AUX).The cavity 201′ also serves as a capacitor to dampen the pulsatile pumpstrokes of the in-process pump PP1 serving the separation chamber 18′.

It is desirable to conduct seal integrity testing of the cassette 28′shown in FIGS. 35 and 36 prior to use. The integrity test determinesthat the pump and valve stations within the cassette 28′ functionwithout leaking. In this situation, it is desirable to isolate thecassette 28′ from the separation chamber 18′. Valves V16 and V17 (seeFIG. 34) in circuit 264′ provide isolation for the whole blood inlet andplasma lines 290′ and 292′ of the chamber 18′. To provide the capabilityof also isolating the red blood cell line 294′, an extra valve fluidactuated station V26 can be added in fluid flow path F7 serving port P7.As further shown in phantom lines in FIG. 43, an addition valve actuatorVA26 can be added to the manifold assembly 226′, to apply positivepressure to the valve V26, to close the valve V26 when isolation isrequired, and to apply negative pressure to the valve V26, to open thevalve when isolation is not required.

VII. Blood Separation Elements A. Molded Processing Chamber

FIGS. 21 to 23 show an embodiment of the centrifugal processing chamber18, which can be used in association with the system 10 shown in FIG. 1.

In the illustrated embodiment, the processing chamber 18 is preformed ina desired shape and configuration, e.g., by injection molding, from arigid, biocompatible plastic material, such as a non-plasticized medicalgrade acrylonitrile-butadiene-styrene (ABS).

The preformed configuration of the chamber 18 includes a unitary, moldedbase 388. The base 388 includes a center hub 120. The hub 120 issurrounded radially by inside and outside annular walls 122 and 124 (seeFIGS. 21 and 23). Between them, the inside and outside annular walls 122and 124 define a circumferential blood separation channel 126. A moldedannular wall 148 closes the bottom of the channel 126 (see FIG. 22).

The top of the channel 126 is closed by a separately molded, flat lid150 (which is shown separated in FIG. 21 for the purpose ofillustration). During assembly, the lid 150 is secured to the top of thechamber 18, e.g., by use of a cylindrical sonic welding horn.

All contours, ports, channels, and walls that affect the bloodseparation process are preformed in the base 388 in a single, injectionmolded operation. Alternatively, the base 388 can be formed by separatemolded parts, either by nesting cup shaped subassemblies or twosymmetric halves.

The lid 150 comprises a simple flat part that can be easily welded tothe base 388. Because all features that affect the separation processare incorporated into one injection molded component, any tolerancedifferences between the base 388 and the lid 150 will not affect theseparation efficiencies of the chamber 18.

The contours, ports, channels, and walls that are preformed in the base388 can vary. In the embodiment shown in FIGS. 21 to 23,circumferentially spaced pairs of stiffening walls 128, 130, and 132emanate from the hub 120 to the inside annular wall 122. The stiffeningwalls 128, 130, 132 provide rigidity to the chamber 18.

As seen in FIG. 23, the inside annular wall 122 is open between one pair130 of the stiffening walls. The opposing stiffening walls form an openinterior region 134 in the hub 120, which communicates with the channel126. Blood and fluids are introduced from the umbilicus 296 into and outof the separation channel 126 through this region 134.

In this embodiment (as FIG. 23 shows), a molded interior wall 136 formedinside the region 134 extends entirely across the channel 126, joiningthe outside annular wall 124. The wall 136 forms a terminus in theseparation channel 126, which interrupts flow circumferentially alongthe channel 126 during separation.

Additional molded interior walls divide the region 134 into threepassages 142, 144, and 146. The passages 142, 144, and 146 extend fromthe hub 120 and communicate with the channel 126 on opposite sides ofthe terminus wall 136. Blood and other fluids are directed from the hub120 into and out of the channel 126 through these passages 142, 144, and146. As will be explained in greater detail later, the passages 142,144, and 146 can direct blood components into and out of the channel 126in various flow patterns.

The underside of the base 388 (see FIG. 22) includes a shaped receptacle179. Three preformed nipples 180 occupy the receptacle 179. Each nipple180 leads to one of the passages 142, 144, 146 on the opposite side ofthe base 388.

The far end of the umbilicus 296 includes a shaped mount 178 (see FIGS.24 and 24A). The mount 178 is shaped to correspond to the shape of thereceptacle 179. The mount 178 can thus be plugged into the receptacle179 (as FIG. 25 shows). The mount 178 includes interior lumens 398 (seeFIG. 24A), which slide over the nipples 180 in the hub 120, to couplethe umbilicus 296 in fluid communication with the channel 126.

Ribs 181 within the receptacle 179 (see FIG. 22) uniquely fit within akey way 183 formed on the mount 178 (see FIG. 24A). The unique fitbetween the ribs 181 and the key way 183 is arranged to require aparticular orientation for plugging the shaped mount 178 into the shapedreceptacle 179. In this way, a desired flow orientation among theumbilicus 296 and the passages 142, 144, and 146 is assured.

In the illustrated embodiment, the umbilicus 296 and mount 178 areformed from a material or materials that withstand the considerableflexing and twisting forces, to which the umbilicus 296 is subjectedduring use. For example, a Hytrel® polyester material can be used.

This material, while well suited for the umbilicus 296, is notcompatible with the ABS plastic material of the base 388, which isselected to provide a rigid, molded blood processing environment. Themount 178 thus cannot be attached by conventional solvent bonding orultrasonic welding techniques to the receptacle 179.

In this arrangement (see FIGS. 24 and 25), the dimensions of the shapedreceptacle 179 and the shaped mount 178 may be selected to provide atight, dry press fit. In addition, a capturing piece 185, formed of ABSmaterial (or another material compatible with the material of the base388), may be placed about the umbilicus 296 outside the receptacle incontact with the peripheral edges of the receptacle 179. The capturingpiece 185 is secured to the peripheral edges of the receptacle 179,e.g., by swaging or ultrasonic welding techniques. The capturing piece185 prevents inadvertent separation of the mount 178 from the receptacle179. In this way, the umbilicus 296 can be integrally connected to thebase 388 of the chamber 18, even though incompatible plastic materialsare used.

The centrifuge station 20 (see FIGS. 26 to 28) includes a centrifugeassembly 48. The centrifuge assembly 48 is constructed to receive andsupport the molded processing chamber 18 for use.

As illustrated, the centrifuge assembly 48 includes a yoke 154 havingbottom, top, and side walls 156, 158, 160. The yoke 154 spins on abearing element 162 attached to the bottom wall 156. An electric drivemotor 164 is coupled via an axle to the bottom wall 156 of the yoke 154,to rotate the yoke 154 about an axis 64. In the illustrated embodiment,the axis 64 is tilted about fifteen degrees above the horizontal planeof the base 38, although other angular orientations can be used.

A rotor plate 166 spins within the yoke 154 about its own bearingelement 168, which is attached to the top wall 158 of the yoke 154. Therotor plate 166 spins about an axis that is generally aligned with theaxis of rotation 64 of the yoke 154.

The top of the processing chamber 18 includes an annular lip 380, towhich the lid 150 is secured. Gripping tabs 382 carried on the peripheryof the rotor plate 166 make snap-fit engagement with the lip 380, tosecure the processing chamber 18 on the rotor plate 166 for rotation.

A sheath 182 on the near end of the umbilicus 296 fits into a bracket184 in the centrifuge station 20. The bracket 184 holds the near end ofthe umbilicus 296 in a non-rotating stationary position aligned with themutually aligned rotational axes 64 of the yoke 154 and rotor plate 166.

An arm 186 protruding from either or both side walls 160 of the yoke 154contacts the mid portion of the umbilicus 296 during rotation of theyoke 154. Constrained by the bracket 184 at its near end and the chamber18 at its far end (where the mount 178 is secured inside the receptacle179), the umbilicus 296 twists about its own axis as it rotates aboutthe yoke axis 64. The twirling of the umbilicus 296 about its axis as itrotates at one omega with the yoke 154 imparts a two omega rotation tothe rotor plate 166, and thus to the processing chamber 18 itself.

The relative rotation of the yoke 154 at a one omega rotational speedand the rotor plate 166 at a two omega rotational speed, keeps theumbilicus 296 untwisted, avoiding the need for rotating seals. Theillustrated arrangement also allows a single drive motor 164 to impartrotation, through the umbilicus 296, to the mutually rotating yoke 154and rotor plate 166. Further details of this arrangement are disclosedin Brown et al U.S. Pat. No. 4,120,449, which is hereby incorporatedherein by reference.

Blood is introduced into and separated within the processing chamber 18as it rotates.

In one flow arrangement (see FIG. 29), as the processing chamber 18rotates (arrow R in FIG. 29), the umbilicus 296 conveys whole blood intothe channel 126 through the passage 146. The whole blood flows in thechannel 126 in the same direction as rotation (which is counterclockwisein FIG. 29). Alternatively, the chamber 18 can be rotated in a directionopposite to the circumferential flow of whole blood, i.e., clockwise.The whole blood separates as a result of centrifugal forces in themanner shown in FIG. 15A. Red blood cells are driven toward the high-Gwall 124, while lighter plasma constituent is displaced toward the low-Gwall 122.

In this flow pattern, a dam 384 projects into the channel 126 toward thehigh-G wall 124. The dam 384 prevents passage of plasma, while allowingpassage of red blood cells into a channel 386 recessed in the high-Gwall 124. The channel 386 directs the red blood cells into the umbilicus296 through the radial passage 144. The plasma constituent is conveyedfrom the channel 126 through the radial passage 142 into umbilicus 296.

Because the red blood cell exit channel 386 extends outside the high-gwall 124, being spaced further from the rotational axis than the high-gwall, the red blood cell exit channel 386 allows the positioning of theinterface between the red blood cells and the buffy coat very close tothe high-g wall 124 during blood processing, without spilling the buffycoat into the red blood cell collection passage 144 (creating anunderspill condition). The recessed exit channel 386 thereby permits redblood cell yields to be maximized (in a red blood cell collectionprocedure) or an essentially platelet-free plasma to be collected (in aplasma collection procedure).

In an alternative flow arrangement (see FIG. 30), the umbilicus 296conveys whole blood into the channel 126 through the passage 142. Theprocessing chamber 18 rotates (arrow R in FIG. 30) in the same directionas whole blood flow (which is clockwise in FIG. 30). Alternatively, thechamber 18 can be rotated in a direction opposite to the circumferentialflow of whole blood, i.e., clockwise. The whole blood separates as aresult of centrifugal forces in the manner shown in FIG. 15A. Red bloodcells are driven toward the high-G wall 124, while lighter plasmaconstituent is displaced toward the low-G wall 122.

In this flow pattern, the dam 384 (previously described) preventspassage of plasma, while allowing passage of red blood cells into therecessed channel 386. The channel 386 directs the red blood cells intothe umbilicus 296 through the radial passage 144. The plasma constituentis conveyed from the opposite end of the channel 126 through the radialpassage 146 into umbilicus 296.

In another alternative flow arrangement (see FIG. 31), the umbilicus 296conveys whole blood into the channel 126 through the passage 144. Theprocessing chamber 18 is rotated (arrow R in FIG. 31) in the samedirection as blood flow (which is clockwise in FIG. 31). Alternatively,the chamber 18 can be rotated in a direction opposite to thecircumferential flow of whole blood, i.e., counterclockwise. The wholeblood separates as a result of centrifugal forces in the manner shown inFIG. 15A. Red blood cells are driven toward the high-G wall 124, whilelighter plasma constituent is displaced toward the low-G wall 122.

In this flow pattern, a dam 385 at the opposite end of the channel 126prevents passage of plasma, while allowing passage of red blood cellsinto a recessed channel 387. The channel 387 directs the red blood cellsinto the umbilicus 296 through the radial passage 146. The plasmaconstituent is conveyed from the other end of the channel 126 throughthe radial passage 142 into umbilicus 296. In this arrangement, thepresence of the dam 384 and the recessed passage 386 (previouslydescribed) separates incoming whole blood flow (in passageway 144) fromoutgoing plasma flow (in passageway 142). This flow arrangement makespossible the collection of platelet-rich plasma, if desired.

In another alternative flow arrangement (see FIG. 32), the passage 144extends from the hub 120 into the channel 126 in a direction differentthan the passages 142 and 146. In this arrangement, the terminus wall136 separates the passages 142 and 146, and the passage 144 communicateswith the channel 126 at a location that lays between the passages 142and 146. In this arrangement, the umbilicus 296 conveys whole blood intothe channel 126 through the passage 146. The processing chamber 18 isrotated (arrow R in FIG. 32) in the same direction as blood flow (whichis clockwise in FIG. 32). Alternatively, the chamber 18 can be rotatedin a direction opposite to the circumferential flow of whole blood,i.e., counterclockwise. The whole blood separates as a result ofcentrifugal forces in the manner shown in FIG. 15A. Red blood cells aredriven toward the high-G wall 124, while lighter plasma constituent isdisplaced toward the low-G wall 122.

In this flow pattern, the passage 144 conveys plasma from the channel126, while the passage 142 conveys red blood cells from the channel 126.

As previously mentioned, in any of the flow patterns shown in FIGS. 28to 32, the chamber 18 can be rotated in the same direction or in anopposite direction to circumferential flow of whole blood in the channel126. Blood separation as described will occur in either circumstance.Nevertheless, it has been discovered that, rotating the chamber 18 inthe same direction as the flow of whole blood in the channel 126 duringseparation, appears to minimize disturbances, e.g., Coriolis effects,resulting in increased separation efficiencies.

EXAMPLE

Whole blood was separated during various experiments into red bloodcells and plasma in processing chambers 18 like that shown in FIG. 28.In one chamber (which will be called Chamber 1), whole bloodcircumferentially flowed in the channel 126 in the same direction as thechamber 18 was rotated (i.e., the chamber 18 was rotated in acounterclockwise direction). In the other chamber 18 (which will becalled Chamber 2), whole blood circumferentially flowed in the channel126 in a direction opposite to chamber rotation (i.e., the chamber 18was rotated in a clockwise direction). The average hematocrit for redblood cells collected were measured for various blood volume samples,processed at different combinations of whole blood inlet flow rates andplasma outlet flow rates. The following Tables summarize the results forthe various experiments.

TABLE 1 (Flow in the Same Direction as Rotation) Number of Blood AverageWhole Blood Average Hematocrit of Samples Processed Hematocrit (%) RedBlood Cells Collected 7 45.4 74.8 4 40 78.8

TABLE 2 (Flow in the Opposite Direction as Rotation) Number of BloodAverage Whole Blood Average Hematocrit of Samples Processed Hematocrit(%) Red Blood Cells Collected 3 43.5 55.5 2 42.25 58.25

Tables 1 and 2 show that, when blood flow in the chamber is in the samedirection as rotation, the hematocrit of red blood cells is greater thanwhen blood flow is in the opposite direction. A greater yield of redblood cells also means a greater yield of plasma during the procedure.

B. Alternative Molded Processing Chamber

FIG. 33 shows a chamber 18′ having a unitary molded base 388′ like thatshown in FIGS. 21 to 23, but in which two flow paths 126′ and 390 areformed. The flow paths 126′ and 390 are shown to be concentric, but theyneed not be. The chamber 18′ shares many other structural features incommon with the chamber 18 shown in FIG. 23. Common structural featuresare identified by the same reference number marked with an apostrophe.

The base 388′ includes a center hub 120′ which is surrounded radially bythe inside and outside annular walls 122′ and 124′, defining betweenthem the circumferential blood separation channel 126′. In thisembodiment, a second inside annular wall 392 radially surrounds the hub120′. The second circumferential blood separation channel 390 is definedbetween the inside annular walls 122′ and 392. This construction formsthe concentric outside and inside separation channels 126′ and 390.

An interruption 394 in the annular wall 122′ adjacent to the dam 384′establishes flow communication between the outside channel 126′ and theinside channel 390. An interior wall 396 blocks flow communicationbetween the channels 126′ and 390 at their opposite ends.

As the processing chamber 18′ rotates (arrow R in FIG. 33), theumbilicus 296 conveys whole blood into the outside channel 126′ throughthe passage 144′. The whole blood flows in the channel 126′ in the samedirection as rotation (which is counterclockwise in FIG. 33).Alternatively, the chamber 18′ can be rotated in a direction opposite tothe circumferential flow of whole blood, i.e., clockwise. The wholeblood separates in the outside channel 126′ as a result of centrifugalforces in the manner shown in FIG. 15A. Red blood cells are driventoward the high-G wall 124′, while lighter plasma constituent isdisplaced toward the low-G wall 122′.

As previously described, the dam 384′ prevents passage of plasma, whileallowing passage of red blood cells into a channel 386′ recessed in thehigh-G wall 124′. The channel 386′ directs the red blood cells into theumbilicus 296 through the radial passage 142′. The plasma constituent isconveyed from the channel 126′ through the interruption 394 into theinside separation channel 390.

The plasma flows circumferentially through the inside channel 390 in adirection opposite to the whole blood in the outside channel 126′.Platelets remaining in the plasma migrate in response to centrifugalforces against the annular wall 124′. The channel 390 directs the plasmaconstituent to the same end of the chamber 18′ where whole blood isinitially introduced. The plasma constituent is conveyed from thechannel 390 by the passage 146′.

C. Another Alternative Molded Processing Chamber

FIGS. 44-46 illustrate a further embodiment of a chamber, which isgenerally indicated at 500 having radially spaced apart inner (low-g)and outer (high-g) side wall portions 502 and 504, respectively, abottom or first end wall portion 506, and a cover or second end wallportion (not illustrated). The wall portions 502 and 504, the bottom506, and the cover together define an enclosed, generally annularchannel 508.

A (whole blood) inlet 510 communicating with the channel 508 is definedbetween opposing interior radial walls 512 and 514. One of the interiorwalls 512 joins the outer (high-g) wall portion and separates theupstream and downstream ends of the channel 508. The interior walls 512and 514 define the inlet passageway 510 of the chamber 500 which, in oneflow configuration, allows fluid to enter the upstream end of thechannel 508 at a location which is adjacent the outer or high-g sidewall portion 504.

A dam or barrier 516 is formed at a downstream end of the channel 508and has upstream and downstream sides 518 and 520 (FIG. 44). The barrier516 extends from the outer side wall portion 504 radially inward to alocation which is spaced from the inner side wall portion 502. Thebarrier 516 will be described in further detail below.

In the embodiment of FIG. 45, the barrier 516 extends for the entireaxial height of the channel 508, except for an underpass 522 located atan intermediate axial position spaced below the top of the channel andabove, but adjacent to, the bottom 506 of the chamber 500. The underpass522 is positioned in the channel 508 and defines an opening orpassageway through or below the barrier 516, thereby allowing forcommunication between the upstream and the downstream sides 518 and 520of the barrier 516. The underpass 522, and particularly the underpassinlet and outlet openings, are preferably located near or in theproximity of the high-g side wall portion 504, where higher density cellcomponents, such as red cells, may accumulate under centrifugal force.More specifically, the high-g side wall portion 504 has a radiallyoutward indent or recess on either side of the barrier 516. As seen inFIG. 44, sections 524 and 526 of the outer side wall portion 504 justupstream and downstream of the barrier 516 extend radially outward from(i.e., are located at a greater radial distance than) a more upstreamsection of the outer side wall portion 504. An outer radial surface ofthe underpass 522 may be formed in part by one or more of these radiallyoutward sections 524 and 526 of the outer side wall portion 504 (whichsections 524 and 526 are shown removed in FIG. 45). An opposed innerradial surface of the underpass 522 (visible in FIG. 45 beneath thebarrier 116) may be formed at a radial location which is approximate tothat of the outer or high-G wall portion 504.

A second flow path, referred to herein as a low-g flow path andgenerally indicated at 528, also communicates between the upstream anddownstream sides 518 and 520 of the barrier 516. As shown in FIG. 44,the low-g flow path 528 is distinguishable from the underpass 522 for anumber of reasons. For one, the low-g flow path 528 is defined betweenthe barrier 516 and the inner side wall portion 502, allowing for fluidflow around, rather than through or below the barrier 516. It will beseen that the low-g flow path 528 is positioned at a more radiallyinward location than the underpass 522, making the low-g flow path 528suitable for accommodating flow of a less dense fluid component, such asplasma, that may accumulate along the inner side wall portion 502, aswill be described in greater detail herein. Further, the illustratedlow-g flow path 528 is positioned adjacent to the top of the channel508, with a bottom or lower axial surface of the low-g flow path 528being defined by an intermediate end wall portion 532, in contrast tothe underpass 522, which is positioned adjacent to the bottom 506 of thechamber 500 (FIG. 45).

As shown in FIG. 44, the low-g flow path 528 may include both non-radialand radial portions or legs 534 and 536, respectively, giving the low-gflow path 528 a generally L-shaped configuration. In the illustratedembodiment, the non-radial or annular portion or leg 534 is defined bythe space between the inner side wall portion 502 and a radially inwardsurface of the barrier 516. The illustrated radial portion or leg 536 isdefined by the downstream side 520 of the barrier 516 and an interiorradial wall extension 538. The interior radial wall extension 538 ofFIGS. 44 and 45 terminates at an outer edge 540 which is located at anintermediate radial location between the inner and outer side wallportions 502 and 504.

The chamber 500 further includes first and second outlets 542 and 544,respectively, which may be defined by opposing surfaces of interiorradial walls. The first (plasma) outlet 542 communicates with thechannel 508 upstream of the barrier 516. The second (red blood cell)outlet 544 communicates with the channel 508 downstream of the barrier516. Both the first and second outlets 542 and 544 extend radiallyinward from the channel 508. The first outlet 542 extends radiallyinward from an opening 546 which, in the illustrated embodiment, islocated at the inner side wall portion 502. The second outlet 544extends radially inward from an opening 548 that communicates with thedownstream side of the barrier 516. In one embodiment, the opening 546of the first outlet 542 is disposed at approximately a 45 degree anglerelative to the opening 548 of the second outlet 544, although otherangles and orientations are also possible.

FIG. 46 shows the relative positions of a radially innermost layer 550,a radially outermost layer 552, and a radially intermediate or interfacelayer 554 during a typical procedure when the chamber 500 is used tofractionate an amount of blood. The radially innermost layer 550 ispositioned adjacent to the inner (low-g) wall portion 502 and, in oneembodiment, will be substantially comprised of plasma. The radiallyoutermost layer 552 is positioned adjacent to the outer (high-g) wallportion 504 and, in one embodiment, will be substantially comprised ofred blood cells. The interface layer 554 is located radiallyintermediate the other layers 550 and 552 and, in one embodiment, willbe substantially comprised of white blood cells and platelets.

The constitution of the various layers illustrated in FIG. 46 may varyaccording to the particular procedure. For example, when the chamber 500is spun at a relatively high speed the radially innermost layer 550 willcomprise substantially cell-free plasma, whereas the innermost layer 550will instead comprise a mixture of plasma and platelets (referred toherein as a “plasma/platelet layer”) when a slower spin speed isemployed. In other procedures, the radially innermost layer 550 may alsocontain an amount of anticoagulant, white blood cells, and/or anon-plasma platelet storage solution.

Regardless of the exact composition of the various layers, the radiallyoutermost layer 552 will flow through the underpass 522 (FIG. 45) to thedownstream side 520 of the barrier 516 and into the opening 548 of thesecond outlet 544, where it exits the channel 508 (FIG. 46). A portionof the radially innermost layer 550 will enter the opening 546 of thefirst outlet 542 and exit the channel 508 therethrough, upstream(approximately 40-45°) of the barrier 516. Another portion of theradially innermost layer 550 will flow past the opening 546 and into thelow-g flow path 528, but is prevented from flowing into the opening 548of the second outlet 544 by the presence of the denser outermost layer552 on the downstream side 520 of the barrier 516. As for the interfacelayer 554, it will engage against the upstream side of the barrier 516and accumulate without exiting the channel 508.

VIII. Red Blood Cell/Platelet/Plasma Collection

The processing chamber 500 of FIGS. 44-46 is particularly well-suitedfor use in a procedure for collecting red blood cells, platelets, andplasma individually or in combination with other components from a bloodsource, and reference will be made thereto for illustrative purposes,however the procedure which follows is not limited to any particularprocessing chamber.

Disposable sets 556 and 558 (FIGS. 47 and 48) may be used in the redblood cell/platelet/plasma collection procedure which follows. Exceptwhere noted otherwise, the individual components of the disposable setsare well-known to those having skill in the art and are essentially asdescribed above with regard to the processing set of FIG. 10.

In one embodiment, the disposable set 556 includes a vascular accessmember 560, such as a needle, an anticoagulant container 562, a redblood cell additive solution container 564, and a saline container 566.The disposable set 556 further includes tubing 568 leading to aconnection device 570 (e.g., a spike in FIG. 47 or a luer connector inFIG. 48) for connection to a platelet storage solution container (notillustrated), if platelet storage solution is to be used. Theillustrated tubing 568 includes an in-line sterility filter 572 of thetype employed in a sub-micron filter, such as a 0.22 μm pore membranefilter, to prevent the passage of viruses or larger microbes, therebypreventing contamination and maintaining an effectively closed system.The disposable set 556 also includes a platelet collection container574, a plasma collection container 576, and a red blood cell collectioncontainer 578 for collecting the blood components that are separated bythe chamber 500. The platelet collection container 574 is illustratedwith an associated in-line leukoreduction filter 580, a gas exhaust orair burp bag 582 for removing an amount of gas from the collectedplatelets (as will be described in greater detail herein), and asampling pack 584 for segregating an amount of the separated plateletsfor subsequent testing and/or tracking purposes according to knownpractice. A red blood cell storage container 586, including segmentedtubing 588 (for segregating an amount of the separated red blood cellsfor subsequent testing and/or tracking purposes) and an in-lineleukoreduction filter 590, is also included for post-separation storageof the red blood cells, as will be described in greater detail herein.

The various components of the disposable set 556 are connected viatubing to a cassette 592, which is shown in greater detail in FIGS. 49and 50. It will be seen that the illustrated cassette 592 has fourteenports PO1-PO14, in contrast to the 13-port cassettes 28 and 28′illustrated in FIGS. 6-9 and 35-36 (respectively) and described withreference to the foregoing blood component collection procedures. The14-port cassette 592 operates generally according to the foregoingdescription of the 13-port cassettes 28 and 28′, except that it includesa total of twenty-six valves VAL1-VAL26 to allow for an additional portPO14 to communicate with other ports. To accommodate the twenty-sixvalves, the corresponding manifold assembly (not illustrated) includestwenty-six valve actuators, similar to the manifold assembly 226′ ofFIG. 43 and works generally according to the foregoing description ofthe manifold assembly 226′.

More particularly, the cassette 592 includes ports PO1-PO14, eachassociated with a component of the disposable set via a length oftubing. Those having skill in the art will appreciate that each port maybe associated with a variety of components and tasks, but in theillustrated embodiment, the first port PO1 is associated with thein-process container 594. The second port PO2 is associated with the redblood cell collection container 578. The third port PO3 is associatedwith the plasma collection container 576. The fourth port PO4 isassociated with the platelet collection container 574. The fifth portPO5 is associated with the (whole blood) inlet 510 of the chamber 500.The sixth port PO6 is associated with the first (plasma) outlet 542 ofthe chamber 500. The seventh port PO7 is associated with the second (redblood cell) outlet 544 of the chamber 500. The eighth port PO8 isassociated with the vascular access member 560. The ninth port PO9 isassociated with the tubing 596 leading to a y-connector 598 for addinganticoagulant to whole blood from the blood source. The tenth port PO10is associated with the anticoagulant container 562. The eleventh portPO11 is associated with the platelet additive solution container (notillustrated). The twelfth port PO12 is associated with the red bloodcell additive solution container 564. The thirteenth port PO13 isassociated with the saline container 566. The fourteenth port PO14 isassociated with the red blood cell storage container 586.

The various ports are fluidly connected to each other by flow pathsdefined by the cassette 592, which flow paths are regulated by valvesVAL1-VAL26. The flow paths and other cavities defined by the raisedcassette walls are shown with stippling in FIG. 50 to distinguish themfrom the walls. The location of the valves within the cassette 592 isbest illustrated in FIG. 49, while the function of each valve can beunderstood with reference to FIG. 51, which is a schematic view of theblood processing circuit 600 defined by the flow paths of the cassette592.

In addition to defining a plurality of flow paths and valves, thecassette 592 further defines a plurality of pumps PU1-PU5 and a filtercavity 602. The pumps and filter cavity correspond generally to thosedescribed above with regard to the cassette 28′ of FIGS. 35-36. Moreparticularly, the first pump PU1 is an in-process pump, the second pumpPU2 is a plasma pump, the third and fourth pumps PU3 and PU4 are donorpumps, and the fifth pump PU5 is an anticoagulant pump. The filtercavity 602 forms a station that may hold a blood filter material toremove clots and cellular aggregations that can form during bloodprocessing.

As for the disposable set 558 of FIG. 48, it is similar to thedisposable set 556 of FIG. 47, with the exception that the salinecontainer is omitted and replaced by a container access member, such asthe illustrated spike 604 and an in-line sterility filter 606. The spike604 may be provided according to known design, being generally hollowwith a sharpened tip suited for piercing a port or membrane of aseparate saline container to fluidly connect the container to thedisposable set 558. As for the filter 606, it may be of the typeemployed in a sub-micron filter to prevent the passage of viruses orlarger microbes, thereby preventing contamination and maintaining aneffectively closed system during association of a saline container withthe disposable set 558. Other disposable sets may also be employedwithout departing from the scope of the present disclosure.

A. Pre-Processing

Prior to processing, an operator selects the “RBC/Platelet/Plasma”protocol from a touch screen display or other user interface system. Ifthe blood source is a donor, the operator then proceeds to enter variousparameters, such as the donor gender/height/weight. In one embodiment,the operator also enters the target yield for the various bloodcomponents. In an exemplary procedure, the pre-selected yields are oneunit each of single dose platelets, packed red cells, and platelet poorplasma. As will be described in greater detail herein, an amount ofplasma may be used to harvest platelets and packed red cells from thechamber and act as a platelet storage fluid, so it may be advantageousto specify an additional amount of plasma (e.g., approximately 335 mlextra-300 ml to harvest and store the platelets and 35 ml to harvest thepacked red cells) to ensure that one unit remains in the plasmacollection container after the platelets and packed red cells have beenharvested.

The operator also selects the collection control system, which may bebased on, for example: (1) the amount of whole blood to process, (2) adonor platelet pre-count (i.e., the amount of platelets in apre-donation sample of the donor's blood) and the target platelet yield,or (3) the target platelet yield. The third option is used when a donorplatelet pre-count is not available and implicates use of an onlineestimator, whereby a volume of whole blood is processed and opticalmeasurements are taken to estimate the platelet pre-count and/or theamount of whole blood that must be processed to achieve the targetplatelet yield. The online estimator will be described in greater detailherein.

Further, before processing begins, any separate containers (e.g., aplatelet storage solution container) are connected to the disposableset, the disposable set is secured to the blood processing system (e.g.,a blood processing system according to the foregoing description ofsystem 10), an integrity check of the disposable set is performed toensure the various components are properly connected and functioning,the blood source is connected to the disposable set (e.g., byphlebotomizing a donor), and the chamber 500 is primed by saline pumpedfrom the saline container 564 by operation of one or more pumps of thecassette 592.

B. Draw Stage

Blood is drawn from a blood source and into the disposable set by atwo-phase process that is illustrated in FIGS. 52A and 52B._Before theblood enters the cassette 592 in either of the phases, an amount ofanticoagulant is added to it. Anticoagulant is pumped from theanticoagulant container 562 (which is connected via tubing to port PO10of the cassette 592), through the cassette flow circuit 600, and outport PO9 of the cassette 592 by operation of the anticoagulant pump PU5.The anticoagulant travels through the tubing 596 connected to the portPO9 and exits through the y-connector 598, where it mixes with bloodflowing from the blood source into the cassette 592 via port PO8.

FIG. 52A schematically illustrates the path through the cassette 592taken by anticoagulated whole blood being pumped from the blood source(which is connected via tubing to port PO8 of the cassette 592), throughthe cassette flow circuit 600, and directly into the chamber 500 (whichis connected via tubing to port PO5 of the cassette 592). The donorpumps PU3/PU3 cooperate with the in-process pump PU1 to flow the bloodthrough the cassette flow circuit 600 in this first phase.

In the phase illustrated in FIG. 52B, anticoagulated blood is pumpedfrom the blood source, through the cassette flow circuit from port PO8to port PO1, and to the in-process container 594 instead of flowingdirectly into the chamber 500 via port PO5. In contrast to the firstphase, the operation of just the donor pumps PU3/PU4 is sufficient forflowing the blood into the in-process container 594 in the phase of FIG.52B. The blood pumped into the in-process container 594 is temporarilystored therein before it is eventually pumped into the chamber 500, aswill be described in greater detail herein.

In one embodiment, blood is drawn from the source by one of the donorpumps PU3/PU4 while the other donor pump PU3/PU4 expels the blood to thechamber 500 or the in-process container 594. This allows forsimultaneous blood draw and pumping to the chamber 500 or the in-processcontainer 594.

The blood may be alternately pumped to the chamber 500 (FIG. 52A) andthen to the in-process container 594 (FIG. 52B) at a particular ratio(e.g., 9:1) to fill both at the same time.

C. Separation Stage

Within the chamber 500, separation of the fluid components occurs basedon density, as shown in FIG. 46, while the chamber spins at a “hardspin” rate of, for example, approximately 4500 RPM. It is noted that theangular velocities used herein conventionally are “two omega” (i.e., thespin speed of the chamber itself) although “one omega” (i.e., the speedat which the umbilicus is orbited around the chamber) may also be used,as well as some combination thereof. Further detail of this separationis set forth in Brown, “The Physics of Continuous Flow Centrifugal SellSeparation,” Artificial Organ, 13(1):4-20 (1989). A higher densitycomponent such as red blood cells is forced towards the outer orhigh-side wall portion in an outermost layer 552 and a lower densitycomponent such as platelet poor plasma is forced towards an inner orlow-g side wall portion in an innermost layer 550. The interface layer554 between the red blood cells and the plasma contains a buffy coatlayer which includes at least a portion of platelets and white bloodcells, although the components of the interface will vary based on theparticular procedure employed.

As the interface is pooling upstream of the barrier 516, fluid may becollected separately from either side of the interface—or both sidesthereof—through the respective outlet 542 or 544 depending on therequirements of the procedure. For example, FIG. 53 schematicallyillustrates the path of whole blood out of port PO5 of the cassette 592and into the chamber 500, with the blood separating into its constituentparts and some platelet poor plasma exiting the chamber 500 through theplasma outlet 542 (per FIG. 46). The plasma exiting the plasma outlet542 flows through tubing and into the cassette 592 via port PO6 of thecassette 592. When the plasma enters the cassette fluid circuit 600, theplasma pump PU2 cooperates with the various valves to convey the plasmato port PO3 of the cassette 592. The plasma exiting port PO3 travelsthrough tubing and into the plasma collection container 576.

Simultaneously, some red blood cells are collected radially outward ofthe interface, exiting the chamber 500 through the red blood cell outlet544 (per FIG. 46). The red blood cells exiting the red blood cell outlet544 flow through tubing and into the cassette 592 via port PO7 of thecassette 592. When the red blood cells enter the cassette fluid circuit600, they are directed to port PO2 of the cassette 592. The red bloodcells exiting the port PO2 travel through tubing and into the red bloodcell collection container 578.

While the plasma and red blood cells are being separated and removedfrom the chamber 500, the barrier 516 allows for accumulation ofplatelets (which are contained in the buffy coat/interface layer 554) inthe channel 508, substantially without the platelets exiting the chamber500 (per FIG. 46).

In one embodiment, the stages of drawing whole blood into the chamberand collecting platelet poor plasma and red blood cells (while retainingbuffy coat in a pool upstream of the barrier 516) are repeated until apredetermined amount of platelets is present in the pooled buffy coat.The amount of platelets that may be pooled in the chamber withoutcausing an overspill or underspill condition depends, in part, upon thedistance between the low-g and high-g walls. In one embodiment, thelow-g and high-g walls are sufficiently spaced from each other to allowfor at least one therapeutic unit of single dose platelets or 6×10¹¹platelets to be pooled upstream of the barrier without causing anoverspill or underspill condition. In another embodiment, the low-g andhigh-g walls are sufficiently spaced from each other to allow for atleast approximately 7×10¹¹ platelets to be pooled upstream of thebarrier without causing an overspill or underspill condition. As anadditional benefit of such a channel configuration, the interface willbe farther spaced from the plasma outlet 542, resulting in less whiteblood cell contamination of the collected platelets.

D. Return Stage

Typically, the amount of blood that must be processed to collect onetherapeutic unit of single dose platelets results in a surplus ofseparated platelet poor plasma and red blood cells. Accordingly,periodically during the platelet pooling process, an amount of thecollected platelet poor plasma and red blood cells may be returned tothe blood source or otherwise conveyed to a recipient.

This may be achieved according to conventional methods, i.e., conveyingthe plasma and red blood cells separately with saline or, moreadvantageously, the returning volumes of plasma and red blood cells maybe interleaved as they are being conveyed to the recipient. Anillustrative interleaving process is shown in FIGS. 54A-54C.

In one phase of the interleaving process (FIG. 54B), a volume ofseparated red blood cells from the red blood cell collection container578 is conveyed to the recipient by operation of the donor pumps PU3 andPU4 of the cassette during a red blood cell pumping interval. Asillustrated, red blood cells from the red blood cell outlet 544 of thechamber 500 and/or saline from the saline container 566 may also beconveyed to the recipient at this time. This phase operates for aselected number of pump strokes to convey a particular volume of redblood cells to the recipient while separated platelet poor plasma fromthe chamber 500 is directed into the plasma collection container 576 byoperation of the cassette.

Once the foregoing phase has been completed, a second phase (illustratedin FIG. 54C) is initiated. In this phase, a volume of separated plasmafrom the plasma collection container 576 is conveyed to the recipient byoperation of the donor pumps PU3 and PU4 of the cassette during a plasmapumping interval. As illustrated, plasma from the plasma outlet 542 ofthe chamber 500 and/or saline from the saline container 566 may also beconveyed to the recipient at this time. This phase operates for aselected number of pump strokes to convey a particular volume of plasmato the recipient while separated red blood cells from the chamber 500are directed into the red blood cell collection container 578 byoperation of the cassette.

These two phases are alternated repeatedly to convey any excess amountsof collected plasma and red blood cells to the recipient. The durationof each pumping interval (i.e., the number of pump cycles) and, hence,the volume of plasma or red blood cells conveyed to the recipient duringa particular phase, depends on the ratio of red blood cells vs. plasmato be returned to the recipient (the “interleaving ratio”), taking intoaccount any other relevant factors as well. For example, if the amountof red blood cells to convey to the recipient is twice the amount ofplasma to convey to the recipient, the system controller will calculatethat the volume of red blood cells to be conveyed in a given phase istwice the volume of plasma to be conveyed in a given phase. With thisinformation, the controller can calculate a 2:1 interleaving ratio andthen actuate the pump system to carry out such interleaving ratio. Ifthe efficiency of pumping red blood cells is approximately equal to theefficiency of pumping plasma, the duration of the red blood cell pumpinginterval should be approximately twice as long as the duration of theplasma pumping interval. On the other hand, if the efficiencies aredifferent, then the relative durations of the pumping intervals will beadjusted to some other ratio so as to carry out the calculatedinterleaving ratio.

It will be appreciated that the interleaved fluid conveyed to therecipient will be similar to anticoagulated blood, having a lowercitrate concentration than plasma, thereby improving donor comfort (ifthe recipient is a human donor), and a lower viscosity than concentratedred blood cells, thereby decreasing the return time. Further, the returntime will also be shorter than known procedures whereby saline isinterleaved with the fluid, as no time is spent returning excess salinevolume.

Regardless of the manner in which plasma and/or red blood cells arereturned to the donor, it will be appreciated that, in a one needlesystem, blood cannot simultaneously be withdrawn from a donor whilereturning fluids to the donor. As such, the direct donor-to-chamber drawphase illustrated in FIG. 52A cannot be employed to supply the chamber500 with additional blood during the return stage. Accordingly, whilethe plasma and/or red blood cells are being returned to the donor, thewhole blood previously supplied to the in-process container 594 (duringthe draw phase illustrated in FIG. 52B) may be pumped into the chamber500, as shown in FIGS. 54B and 54C, allowing for non-stop processing.

E. Red Blood Cell/Platelet Flush Stage

At the end of the platelet pooling process and when it has beendetermined that the required amounts of plasma, red blood cells, andplatelets are present in the system, it may be advantageous for anunderspill condition to be imposed upon the fluid components. Theoperation of the cassette 592 to cause an underspill condition is shownin FIG. 55A. The underspill condition may be forced by stopping thein-process pump PU1 of the cassette 592 and reversing the plasma pumpPU2, thereby causing plasma to be pulled from the plasma collectioncontainer 576 (which is connected via tubing to port PO3 of the cassette592) and into the cassette flow circuit 600. The continued reverseoperation of the plasma pump PU2 directs the plasma through the cassetteflow circuit 600 and out the cassette port PO6, causing it to return tothe chamber 500 through the plasma outlet 542. The plasma entering thechamber 500 pushes the fluid components in the channel 508 toward thehigh-g wall 504, thereby displacing red blood cells and buffy coat intothe red blood cell outlet 544 (which is connected via tubing 608 to portPO7 of the cassette 592). As described previously, the presence of buffycoat materials in the red blood cell outlet 544 constitutes anunderspill condition.

An optical sensor (such as the sensor 336 described above) associatedwith the tubing 608 connecting the red blood cell outlet 544 to port PO7of the cassette 592 detects that a portion of the interface/buffy coatlayer is exiting the outlet, which usually has red blood cells exitingtherethrough. Such underspill condition is empirically determined basedon the optical transmissivity of light through the components in theoutlet tubing 608. The optical sensor data is converted to a hematocrit.A decrease in hematocrit of the fluid moving through the outlet tubing608 registers as an underspill condition.

Forcing an underspill condition allows the interface to be forcedradially outward as compared to the radial location of the interfaceduring normal collection operation. The underspill condition allowsremoval of red blood cells into the red blood cell collection container578 (which is connected via tubing to port PO2 of the cassette 592)until the resulting fluid in the chamber 500 has a hematocrit in atarget range of, for example, approximately 20 to 40 percent.

The forced underspill may be followed by an “add RBC” phase to return acontrolled amount of packed red cells from the red blood cell collectioncontainer 578 to the chamber 500, thereby ensuring that the optimalamount of red blood cells is present in the chamber 500. FIG. 55Billustrates the operation of the cassette 592 during an “add RBC” phase.Such a procedure may be achieved by returning the plasma pump PU2 to itsforward pumping direction, causing platelet poor plasma to flow out ofthe plasma outlet 542 of the chamber 500 (which is connected via tubingto port PO6 of the cassette 592) and into the cassette flow circuit 600.The plasma is directed through the cassette flow circuit 600, outcassette port PO3, and into the plasma collection container 576.Simultaneously, flow into the chamber 500 via the whole blood inlet 510is stopped which, when combined with the plasma being removed from thechamber 500 via the plasma outlet 542, has the effect of drawing thelast-exiting fluid from the cassette 592 via port PO7, through the redblood cell outlet 544, and back into the chamber 500.

Once a desired hematocrit level is achieved in the chamber 500, thefluid in the chamber 500 is advantageously kept within the desiredhematocrit range. For example, the flow of separated plasma out of thechamber 500 via the plasma outlet 542 may be stopped and/or the flow ofseparated red blood cells from the chamber 500 via the red blood celloutlet 544 may also be stopped. Such flow may be stopped by operation ofthe cassette valves and/or by stopping operation of one or more cassettepumps, such as the plasma pump PU2. The in-process pump PU1 may continueto operate, although it may be advantageous for it to be operated at alower flow rate.

At this time, the excess collected red blood cells and plasma may beconveyed to a recipient (as described above), followed by therecipient/donor being disconnected from the system. An additional amountof red blood cells may be conveyed to the recipient, with theunderstanding that the red blood cell harvesting stage (which will bedescribed in greater detail herein) will ultimately bring the amount ofcollected red blood cells up to the target yield.

F. Recombination Stage

The exemplary method further includes the recombination of the separatedfluid components within the chamber. FIGS. 56A and 56B illustrate theoperation of the cassette 592 during the recombination stage. In oneembodiment, recombination is performed by rotation of the chamber 500 inboth clockwise and counterclockwise directions, whereby the chamber 500is rotated alternately in clockwise and counterclockwise directions oneor more times. During this recombination stage, the valves VAL17 andVAL19 associated with the plasma outlet 542 (which is connected viatubing to port PO6 of the cassette 592) are closed. With the plasmaoutlet 542 effectively closed, the contents of the chamber 500 areforced to exit or enter the chamber 500 via the whole blood inlet 510and/or the red blood cell outlet 544. The donor pumps PU3 and PU4 andthe in-process pump PU1 of the cassette 592 are operated to cycle theblood components into and out of the chamber 500, as generallyillustrated in the two-phase process of FIGS. 56A and 56B.

In the phase illustrated in FIG. 56A, the blood components present inthe donor pumps PU3 and PU4 are pumped through the cassette flow circuit600 to the in-process pump PU1. In the phase illustrated in FIG. 56B,the blood components present in the in-process pump PU1 are pumpedthrough the chamber 500 (in through the whole blood inlet 510 viacassette port PO5 and out the red blood cell outlet 544 via cassetteport PO7) and into the donor pumps PU3 and PU4. These phases alternateas the chamber 500 is rotated alternately in clockwise andcounterclockwise directions.

The recombination stage results in a uniform blood-like mixture whichincludes plasma, red blood cells, platelets, and white blood cellshaving an approximate chamber hematocrit as previously described. Therecombination stage may last approximately one to three minutes,although this time period may vary. The rotation of the chamber ineither direction may be at a rate much lower than the rate of rotationduring initial separation of the components and may be, for example, inthe range of approximately 300 to 600 RPM, although other rates ofrotation are possible.

G. Platelet Storage Solution Prime Stage

If a platelet storage fluid other than plasma (e.g., PAS III) is to beused for storing the separated platelets, as will be described ingreater detail herein, it may be advantageous to initiate a “plateletstorage solution prime” stage after the recombination stage. Theoperation of the cassette 592 during such a stage is illustrated in FIG.57. In such a stage, an amount of (non-plasma) platelet storage solutionis pumped from a platelet storage solution container (which is connectedvia tubing to port PO11 of the cassette 592), through the cassette flowcircuit 600, and to the in-process container 594 (which is connected viatubing to port PO1 of the cassette 592) by the plasma pump PU2. Thismoves any air from the platelet storage solution container into thein-process container 594, ensuring that it will not remain in the flowpath during the processing steps which follow.

An amount of (non-plasma) platelet storage solution may be pumped intothe chamber to displace some of the plasma out of the plasma outlet 542,through the cassette flow circuit 600, and into the plasma collectioncontainer 576. This may be advantageous if it is desired for theresulting platelet storage solution to have a higher non-plasma plateletstorage solution to plasma ratio than what is typically achieved by thepresent procedure.

H. Recirculation Stage 1. Recirculation Phase 1

After a sufficient recombination period, the rotor is then restarted torotate the chamber in a uniform direction, with the flow within thechamber being generally directed from the inlet 510 to the first andsecond outlets 542 and 544 (although fluid is still prevented fromexiting the chamber via the plasma outlet 542). The specific speed ofthe rotor may vary, but may be a “slow spin” of approximately 2500-2700RPM, which separates a red blood cell layer from a layer containingplasma and platelets. During this time, the valves VAL17 and VAL19associated with cassette port PO6 are closed, effectively closing theplasma outlet 542 and forcing the fluid in the chamber 500 to exit viathe red blood cell outlet 544 (which is connected via tubing to port PO7of the cassette 592) and flow into the donor pumps PU3 and PU4,identical to the second phase of the recombination stage shown in FIG.56B. The donor pumps PU3 and PU4 pump the fluid through the cassetteflow circuit 600 to the in-process pump PU1 (identical to the firstphase of the recombination stage shown in FIG. 56A). Finally, thein-process pump PU1 pumps the fluid out of port PO5, through the wholeblood inlet 510, and back into the chamber inlet 510. This phase of therecirculation stage continues for a sufficient time to allow the redblood cell layer to settle within the chamber.

2. Recirculation Phase 2

After the red blood cell layer has settled within the chamber, VAL 17 isopened, as shown in FIG. 58A, allowing flow through cassette port PO6and effectively re-opening plasma outlet 542 (which is connected viatubing to port PO6). During this phase, the red blood cell layercontinues exiting the chamber via the red blood cell outlet 544, flowinginto the cassette flow circuit 600 via port PO7, and being directed toone of the donor pumps PO3. With the plasma outlet 542 re-opened, thelayer including plasma and platelets (and any non-plasma plateletstorage solution) is allowed to exit the chamber therethrough and enterthe cassette flow circuit 600 via port PO6. The plasma/platelet layer isdirected from port PO6 to the plasma pump PU2, as shown in FIG. 58A.

Thereafter, the contents of the donor pump PU3 (i.e., the red blood celllayer) and the plasma pump PU2 (i.e., the plasma/platelet layer) arepumped through the cassette flow circuit 600 and into the in-processpump PU1 (FIG. 58B), where they are recombined. The in-process pump PU1subsequently pumps the combined fluids out of the cassette 592 via portPO5 and back to the chamber 500 (FIG. 58A). These sub-phases alternate,thereby creating a recirculation loop into and out of the chamber.

During recirculation, no plasma, platelets, or red blood cells arecollected. The platelet concentration in the plasma/platelet layergenerally increases during this phase, with platelets from the interfacebecoming suspended in the plasma.

Recirculation of the components continues until an optical sensor (suchas the sensor 334 described above) associated with the tubing 610connecting the plasma outlet 542 and cassette port PO6 detects aplasma/platelet layer which has a desired concentration of platelets andwhich is visually low in red blood cells. As discussed above, thehematocrit of the recirculated mixture is approximately between 20-40percent. Recirculation may also be modified so as to recirculate onlyone of the components, either plasma or red blood cells, as desired.

During the recirculation stage, an illustrative pump flow rate ratio ofthe in-process pump PU1 and plasma pump PU2 is 60/40, although otherpump rates may be used depending on the particular conditions of thesystem. Recirculation may also allow an increasing concentration ofwhite blood cells to settle to the interface between the plasma/plateletlayer and the red blood cells. Such pump ratio has also been found tohave a direct influence on the number of white blood cells thatcontaminate the plasma/platelet layer and the overall plateletconcentration collection efficiency. By way of example and notlimitation, FIGS. 59A and 59B show a collected fluid having a higherconcentration of platelets (FIG. 59A) and a lower concentration of whiteblood cells (FIG. 59B). In FIGS. 59A and 59B, such fluid was collectedfrom a chamber having approximately 120 cm² surface area, which wasoperated at a speed of approximately 2500 RPM with a chamber hematocritof approximately 25%. Other collection efficiencies may be developed fordifferent chamber surface areas, centrifugal speeds and chamberhematocrits.

Recirculation of the plasma/platelet layer may continue for severalminutes (approximately two to four minutes in one embodiment), whichduration may vary depending upon the particular procedure. During thistime, the content of the plasma/platelet layer in the tubing 610associated with the plasma outlet 542 may be monitored by theaforementioned optical sensor. For best results, this monitoring istypically delayed until the plasma/platelet layer is substantiallyuniform. The sensor can detect the presence of platelets in the plasma,and the data collected by the sensor can be used during recirculation tocalculate a number of quantities. Those having skill in the art willappreciate that the plasma/platelet layer will have a higher plateletconcentration than typical “platelet rich plasma” (i.e., aplasma/platelet layer that is formed by subjecting whole blood to a“soft spin” without the prior removal of an amount of platelet poorplasma), so the signal will be stronger and the resulting data will tendto be more reliable than data collected by observing typical “plateletrich plasma.”

Among the various quantities that can be calculated, the data collectedby the optical sensor can be used to estimate the current plateletyield. The difference between a baseline optical density (i.e., theoptical density of plasma substantially free of cellular components) andthe detected optical density of the plasma/platelet layer is indicativeof the platelet concentration of the plasma/platelet layer, so a“snapshot” of the platelet content can be estimated by comparing the twovalues over a period of time and then integrating the area therebetweenduring that time. The integrated value can be extrapolated to the totalvolume of blood processed to estimate the current platelet yield.

When the current platelet yield is known, the platelet pre-count of thedonor can be estimated. This may be estimated, for example, byconsidering the amount of detected platelets and the volume of bloodthat has been processed (i.e., the current platelet yield), thencomparing those values (along with any other necessary information, suchas donor hematocrit, weight, and gender, for example) to empirical dataindexing such values with known platelet pre-counts. These calculationsmay be performed by the software of the system controller or the datamay be transmitted to an external integrator before the results arereturned to the system as a platelet pre-count.

This information may be used to calculate a number of other values, forexample, the volume of blood to be processed to collect a target amountof platelets. In one embodiment, this is calculated by feeding thecalculated platelet pre-count, the target platelet yield, and any othernecessary information (such as donor hematocrit, weight, and gender)into a predictor that calculates the volume of blood to be processed. Ifthe calculated volume is greater than the volume of blood in the system,then the process may be modified to include additional draw stages todraw additional blood from the donor or the system may give the operatorthe option to collect less platelets than the target amount.

This information may also be used to calculate the processing timerequired to collect a target amount of platelets using, for example, acalculation process similar to that described previously with regard tothe volume of blood to be processed to collect a target amount ofplatelets. If the calculated processing time exceeds a selected“maximum” processing time (due, for example, to a donor having abelow-average platelet pre-count), the system may present the operatorwith a number of options. For example, in one embodiment, the expectedproducts are one unit of single dose platelets, one unit of red bloodcells, and one unit of plasma. In this case, the operator can be giventhe option of collecting only the red blood cells and plasma (whilereturning the platelets to the donor) or collecting the full amounts ofred blood cells and plasma and a partial dose of platelets.Alternatively, the choice to modify the expected products during theprocedure may be made by the system controller rather than by theoperator.

Other adjustments may also be made to the collection procedure duringprocessing for optimal performance. For example, in one embodiment, thetarget range for collected platelets is between 3.0×10¹¹ (the industryrequirement) and 4.7×10¹¹ (the maximum platelet capacity of an exemplaryplatelet collection container). If it is determined that the plateletyield will exceed the target value or range, the spin speed of thechamber may be increased to sediment some of the platelets out of theplasma/platelet layer. As an additional benefit, increasing the spinspeed will also cause some white blood cells in the plasma/plateletlayer to sediment out of the layer, thereby reducing the white bloodcell content of the plasma/platelet layer. Alternatively, if it isdetermined that the platelet yield will fall below a targeted value orrange, the spin speed of the chamber may be decreased to pull moreplatelets from the interface into the plasma/platelet layer.

Yet another option is to use the calculated platelet yield to calculatethe optimal amount of platelet storage fluid (e.g., platelet poor plasmaor non-plasma storage solution or a combination thereof) to use forstoring the platelets.

Those having skill in the art will appreciate that other quantities canalso be calculated by measuring the amount of platelets in the outlettubing 610 during this recirculation stage.

I. Platelet Harvesting Stage

After the recirculation stage and any additional blood processing stages(if it is determined during the recirculation stage that additionalblood collection and processing are required to collect the targetamount of platelets), a platelet harvesting stage is initiated. In theplatelet harvesting stage, the plasma/platelet layer is pumped out ofthe chamber 500 via the plasma outlet 542 and into the plateletcollection container 574. This is achieved by continuing the immediatelypreceding recirculation stage, but adding a platelet storage fluid(platelet poor plasma from the plasma collection container 576 and/ornon-plasma storage solution from the platelet storage solutioncontainer) to the circulating fluid. The additional fluid replaces thefluid volume lost within the chamber 500 due to collection of theplasma/platelet layer.

In particular, as shown in FIG. 58B, the contents of the plasma pump PU2(i.e., the plasma/platelet layer) and the contents of the donor pump PU3(i.e., the red blood cell layer) flow to the in-process pump PU1. Themixed contents of the in-process pump PU1 are then pumped out ofcassette port PO5 and into the chamber 500, as packed red cells exit thechamber 500 via the red blood cell outlet 544 and are pumped throughcassette port PO7 into the donor pump PU3 (FIGS. 60A/60B).Simultaneously, the plasma/platelet layer exits the chamber 500 via theplasma outlet 542 and is pumped through cassette port PO6, through thecassette flow circuit 600, and out port PO4 to the platelet collectioncontainer 574 (FIGS. 60A/60B). Rather than being filled with theplasma/platelet layer (as in the recirculation stage), the plasma pumpPU2 is filled with a platelet storage fluid. In one embodiment,illustrated in FIG. 60A, the plasma pump PU2 is filled with plasma fromthe plasma collection container 576 (which is connected via tubing toport PO3 of the cassette 592). In another embodiment, illustrated inFIG. 60B, the plasma pump PU2 is instead filled with non-plasma storagesolution from the platelet storage solution container (which isconnected via tubing to port PO11 of the cassette 592).

With this additional fluid in the plasma pump PU2, the contents thereofand the contents of the donor pump PU3 again flow into the in-processpump PU1 (FIG. 58B). Finally, the in-process pump PU1 is emptied intothe chamber 500 through the whole blood inlet 510 (which is connectedvia tubing to port PO5 of the cassette 592), with the plasma/plateletlayer being displaced out of the plasma outlet 542 and into the cassetteflow circuit 600 via port PO6 (alternatively illustrated in FIGS. 60Aand 60B). Once in the cassette 592, the plasma/platelet layer is pumpedfrom port PO6 to port PO4 and to the platelet collection container 574.Simultaneously, the packed red cells flow from the red blood cell outlet544, into the cassette flow circuit 600 via port PO7, and through thecassette flow circuit 600 to the donor pump PU3 (alternativelyillustrated in FIGS. 60A and 60B). These sub-phases alternate (i.e.,between the sub-phase illustrated in FIG. 58B and the sub-phaseillustrated in FIGS. 60A/60B), thereby creating a recirculation loopinto and out of the chamber, with an amount of the plasma/platelet layerbeing collected during each iteration of the loop.

The sub-phases illustrated in FIGS. 60A and 60B may be practicedindependently (e.g., employing only the sub-phase of FIG. 60A incombination with the sub-phase of FIG. 58B to harvest and storeplatelets in platelet poor plasma) or combined during a given procedure.For example, the platelet harvesting stage may following a repeatingloop from the sub-phase illustrated in FIG. 58B, to the sub-phaseillustrated in FIG. 60A, to the sub-phase illustrated in FIG. 58B, tothe sub-phase illustrated in FIG. 60B, and finally back to the beginningof the loop. Such a harvesting loop may be modified depending on theparticular process, for example, by employing a loop initiating two FIG.60A sub-phases for every FIG. 60B sub-phase that is initiated. In yetanother embodiment, non-plasma storage solution is used to displace andstore platelets (i.e., the FIGS. 58B and 60B sub-phases are alternated)until a target amount of storage solution has been used, at which timeplatelet poor plasma is used to displace and store the platelets (i.e.,the FIGS. 58B and 60A sub-phases are alternated) until the targetplatelet yield is achieved.

One phenomenon that has been observed is the plasma/platelet layerbecoming contaminated by white blood cells during the plateletharvesting stage. Rather than a uniform or continuous contamination, thewhite blood cells typically spill into the plasma/platelet layer in asingle “burst” shortly after the harvesting stage begins. A diagram ofthe white blood cell contamination is shown in FIG. 61A. Typically, this“burst” is detected approximately one minute after the beginning of theharvesting stage, which has led to the belief that the “burst” is causedby non-plasma storage solution reaching the chamber. The non-plasmastorage solution is less dense than the plasma/platelet layer, and thisslight difference in physical properties may disturb the interface,causing white blood cells to spill through the plasma outlet 542.Typically, around the two-minute mark of the harvesting stage, the whiteblood cell concentration (as detected by the optical sensor associatedwith the outlet tubing 610) will begin to decrease and, around thethree-minute mark, the white blood cell concentration will be at orbelow the level at the beginning of the platelet harvesting stage.

It is known that increasing the spin speed of the chamber 500 will forcemore white blood cells to sediment from the plasma/platelet layer intothe interface, so the “burst” may be combated by spinning the chamber500 at a higher speed during the harvesting stage. However, increasingthe spin speed also degrades the platelet recovery, as some of theplatelets will be sedimented into the interface with the white bloodcells. Accordingly, it may be advantageous to operate the chamber at anelevated spin speed only during the beginning of the platelet harvestingstage (i.e., during the time of the “burst”) and decrease the speedduring the remainder of the stage, as is shown in FIGS. 61B-61D. In anexemplary embodiment, the recirculation stage is carried out at a spinspeed of approximately 2700 RPM, which may be gradually or incrementallyincreased to an elevated speed (around 3000 RPM in one embodiment)before being decreased to the original spin speed.

FIGS. 61B and 61C illustrate two different spin speed profiles forcombating the “burst.” In the embodiment of FIG. 61B, the spin speed isgradually increased at a rate of approximately 200 RPM/min to a maximumspin speed of approximately 3000 RPM at approximately one and a halfminutes after the beginning of the harvesting stage. Thereafter, thespin speed is gradually decreased at a rate of approximately 200 RPM/minto return to the original spin speed of approximately 2700 RPM by thethree-minute mark of the harvesting stage. The spin speed remains atapproximately 2700 RPM for the rest of the harvesting stage.

In the embodiment of FIG. 61C, the spin speed is increased at a rate ofapproximately 300 RPM/min, such that the chamber will be spinning atapproximately 3000 RPM at the time that the “burst” typically occurs.The spin speed remains at 3000 RPM for approximately one minute andthen, at the two-minute mark, the spin speed is ramped down at, forexample, 300 RPM/min to the original spin speed, where it remains forthe rest of the harvesting stage.

FIG. 61D illustrates yet another possible spin speed profile. Thisprofile is similar to that of FIG. 61C, but the spin speed is ultimatelyramped down to a speed below the spin speed at the beginning of theharvesting stage, for example 2500 RPM. This may be advantageous tocompensate for the decreased collection efficiency during the elevatedspin speed and may be employed without risking additional contamination,as it has been observed that the white blood cell concentration detectedby the optical sensor is relatively low after the three-minute mark ofthe harvesting stage. These illustrated spin speed profiles are merelyillustrative, and other “burst”-combating spin speed profiles may alsobe employed without departing from the scope of the present disclosure.This principle may also be employed to combat other contaminationprofiles, such as those characterized by multiple “bursts” or the like.

In yet another embodiment, the platelet harvesting stage may be modifiedby incrementally decreasing the spin speed of the chamber while theplasma/platelet layer is being collected. So decreasing the spin speedwill move the interface closer to the low-g wall 502, thereby pushingthe platelets toward the plasma outlet 542 and increasing the efficiencyof the system. This embodiment is best employed when only platelet poorplasma is used to collect and store the platelets, as the use ofplatelet poor plasma alone will typically avoid the aforementioned“burst” of white blood cells.

Regardless of the particular chamber spin speed profile that is employedduring the platelet harvesting stage, it may be advantageous to continuemonitoring the platelet concentration of the plasma/platelet layer as itis being collected to determine when the target amount of platelets hasbeen collected. The yield can be calculated, for example, by comparing acurve plotting a baseline optical density (of a plasma layer containingsubstantially no cellular components) to a curve plotting the detectedoptical density. The difference between the two values is indicative ofthe platelet concentration of the plasma/platelet layer, so the amountof platelets collected can be calculated by comparing the two valuesduring the platelet harvesting stage and then integrating the areabetween the curves periodically. If the optical reading differs fromthat which is expected, the spin speed of the chamber may be changed tobring it back in line (e.g., by increasing the spin speed to sedimentplatelets from the plasma/platelet layer and decrease the opticaldensity of the plasma/platelet layer or decreasing the spin speed topull platelets into the plasma/platelet layer from the interface andincrease the optical density of the plasma/platelet layer). The opticalreadings taken during the platelet harvesting stage or the finalplatelet yield calculated during the recirculation stage (describedabove) may be used to make on-the-fly adjustments to the amount ofstorage fluid ultimately added to the platelet collection container.

When the target platelet yield has been reached, the system may operateto flow plasma and/or non-plasma storage solution directly to theplatelet collection container (bypassing the chamber) if need be.

Although the majority of leukocytes in the plasma/platelet layer willsediment therefrom during the aforementioned recirculation stages, someleukocytes typically remain in the collected fluid. The illustrateddisposable sets 556 and 558 (FIGS. 47 and 48, respectively) show anin-line leukoreduction filter 580 between the cassette 592 and theplatelet collection container 574. In such embodiments, theplasma/platelet layer that is pumped out of the chamber 500 by theplasma pump PU2 is pumped through the leukoreduction filter 580 and intothe platelet collection container 574 while the chamber 500 is stillspinning and processing the blood components. In one example, areduction of white blood cells from approximately 1.0×10⁷ toapproximately 1.0×10⁴ on account of an in-line leukoreduction filter wasobserved.

J. Red Blood Cell Harvesting Stage

When the platelet harvesting stage is complete, the system continueswith a red blood cell harvesting stage, which is illustratedschematically in FIG. 62. During this stage, the valves VAL17 and VAL19associated with cassette port PO6 are closed, effectively closing theplasma outlet 542, and the spin speed of the chamber 500 is increased toa “hard spin” of, for example, approximately 4500 RPM. The in-processpump PU1 delivers platelet poor plasma from the plasma collectioncontainer 576 (which is connected via tubing to port PO3 of the cassette592) to the chamber 500 via the whole blood inlet 510 (which isconnected via tubing to port PO5 of the cassette 592). The incomingplasma forces the packed red blood cells out of the red blood celloutlet 544 and into the cassette flow circuit 600 via port PO7. The redblood cells are directed through the cassette flow circuit 600, out ofport PO2, and to the red blood cell collection container 578.

K. Post-Processing Stage

After the platelets and red blood cells have been collected, any of anumber of post-processing procedures may be initiated, a number of whichare described below.

1. Burping the Platelet Product

As a result of the manufacturing process, there may be some air presentin the tubing leading from the cassette 592 to the platelet collectioncontainer 574 or in the associated leukoreduction filter 580, whichmeans that the plasma/platelet layer passing through the filter 580 willforce the air into the platelet collection container 574. For a numberof well-known reasons, it is desirable to avoid air in the collectioncontainer. Accordingly, the platelet collection container 574 mayinclude a length of tubing leading to a gas exhaust or air burp bag 582,as shown in FIGS. 47 and 48. Air is removed from the collected plateletproduct by closing the inlet tubing (typically with a clamp) andsqueezing the flexible container 574, thereby forcing air out of thecontainer 574 and into the air burp bag 582. The operator watches thetubing to the air burp bag 582 to ensure that little to no plateletproduct leaves the container 574 during this de-aeration or “burping”process.

Alternatively, rather than employing a manual burping process, anautomated burping process is possible. FIGS. 63A-63D show anillustrative automated de-aeration or burping process. First, a pump 612is operated in a forward direction to pump fluid “F” through a conduit614 to a flexible collection container 616 (FIG. 63A). This first stepis optional, as the following operations may be performed with anyflexible container with an amount of fluid and gas, regardless of howthe fluid and gas were transferred into the container. When all of thefluid “F” has been pumped into the collection container 616, there willbe an amount of air “A” above the fluid “F.” To remove the air, the pump612 is operated in a reverse direction to pull the air “A” and fluid “F”back out of the collection container 616 (FIG. 63B). As air “A” andfluid “F” are being removed from the collection container 616, anoptical sensor 618 (e.g., a QProx™ sensor from Quantum Research GroupLtd. of Hamble, England) monitors the conduit 614. The optical sensor618 is adapted to distinguish between air and fluid in the conduit 614and may be configured according to known design.

When the optical sensor 618 detects the air-fluid interface “I” in theconduit 614 (FIG. 63C), it signals for the pump 612 (or signals to anintermediary, such as a controller, that commands the pump) to stopoperating in the reverse direction and switch to operating in theforward direction. The pump 612 continues to run in the forwarddirection until the fluid “F” in the conduit 614 has been returned tothe collection container 616, with the air “A” remaining in the conduit614 (FIG. 63D). The volume of fluid “F” in the conduit 614 can becalculated, based on the geometry of the conduit 614 and the distancebetween the collection container 616 and the sensor 618, so the pump 612may be operated for a predetermined number of forward cycles (each ofwhich returns a calculable volume of fluid “F” to the collectioncontainer 616) to return the fluid “F” to the collection container 616.It will be appreciated that such an automated process may be employed toremove air from the collected blood component(s) in any of thecollection containers described herein.

This automated burping process may be variously modified withoutdeparting from the scope of the present disclosure. For example, ratherthan performing a predetermined number of pump cycles to return fluidfrom the conduit 614 to the collection container 616, the operator maybe given the option (via a touch screen or other user interface system)to enter the number of cycles to perform. In another embodiment, theoperator may be given the option to order a pump cycle (either a forwardor reverse cycle) at the touch of a button or icon. In yet anotherembodiment, the system controller may automatically burp the collectioncontainer and thereafter give the operator the option of confirming thatthere has been sufficient purgation and, if not, allow the operator toorder individual or multiple pump cycles.

2. Red Blood Cell Storage and Filtration

The disposable sets 556 and 558 illustrated in FIGS. 47 and 48 include ared blood cell storage container 586, which is distinct from the redblood cell collection container 578. For reasons that are well-known, itis beneficial to add an additive solution (e.g., Adsol® or SAG-M) topacked red cells. While it is possible to add an additive solution froman additive solution container 564 to the packed red cells in the redblood cell collection container 578 after processing, doing so requiresan additional mixing step that is typically performed manually. Ratherthan carrying out such a procedure, it may be advantageous toautomatically mix the packed red cells and additive solution as they areflowing into the red blood cell storage container 586. This can beachieved, for example, by an interleaving process whereby a first phaseof pumping an amount of packed red cells from the red blood cellcollection container 578 to the red blood cell storage container 586 isalternated with a phase of pumping an amount of additive solution fromthe additive solution container 564 to the red blood cell storagecontainer 586. By alternating the two phases, the contents of the redblood cell storage container 586 are automatically mixed withoutrequiring manual intervention.

The above mixing procedure is illustrated in greater detail in FIGS.64A-64C. FIG. 64A shows an additive solution prime stage, whereby thedonor pumps PU3 and PU4 are operated to flow additive solution from theadditive solution container 564 into the cassette flow circuit 600 viaport PO12. The solution is pumped through the cassette flow circuit 600by the donor pumps PU3 and PU4 to port PO2 and out of the cassette 592to the red blood cell collection container 578. This phase acts to primethe tubing between the additive solution container 564 and the cassette592. Next, FIG. 64B shows the donor pumps PU3 and PU4 operating to flowpacked red cells from the red blood cell collection container 578 intothe cassette flow circuit 600 via port PO2, through the cassette 592,and then out port PO14 to the red blood cell storage container 586.

As shown in the disposable sets 556 and 558 of FIGS. 47 and 48, theremay be an in-line leukoreduction filter 590 associated with the tubingbetween the cassette 592 and the red blood cell storage container 586,thereby filtering the packed red cells as they are pumped through theleukofilter 590 and to the red blood cell storage container 586.

After a certain number of red blood cell pumping cycles, the systemswitches to an additive solution pumping phase illustrated in FIG. 64C.In this phase, additive solution is pumped from the additive solutioncontainer 564, through the cassette flow circuit 600, and into the redblood cell storage container 586 (i.e., into the cassette 592 throughport PO12 and out through port PO14). This phase continues for a certainnumber of pump cycles and then the phases of pumping packed red cells(FIG. 64B) and additive solution (FIG. 64C) to the red blood cellstorage container 586 are alternated until the red blood cell collectioncontainer 578 is empty.

If the amount of additive solution required to achieve a target ratio(2.1:1 in one embodiment) has not been pumped to the red blood cellstorage container 586 by the time the red blood cell collectioncontainer 578 is empty, a final phase of pumping additional additivesolution to the red blood cell storage container 586 may be initiated.

3. Platelet Poor Plasma Storage and Filtration

In addition to filtering the collected packed red cells, any plateletpoor plasma remaining in the plasma collection container 576 may besimilarly pumped through a leukoreduction filter and stored in a plasmastorage container (not illustrated).

A manual or automated burping process (e.g., the automated processdescribed above with regard to the collected platelets) may be employedto remove any excess air from the filtered plasma and/or packed redcells. If the disposable set is not provided with an air burp bag for aparticular filtered blood component, the air may be directed to one ofthe empty containers, for example, to the empty red blood cellcollection container 578.

When the various blood components are in their final storage containers,the containers are typically weighed or otherwise analyzed to confirmthat the target yield has been achieved and thereafter separated fromthe disposable set, which is discarded. Depending on the configurationof the disposable set, samples of the various components may also betaken using, for example in the disposable sets 556 and 558 of FIGS. 47and 48, a sampling pack 584 for the harvested platelets and a length ofsegmented tubing 588 for the harvested packed red cells.

L. Other Modifications

Various modifications to the above-described method are possible. Onemodification includes operating the in-process pump PU1 between at leasttwo different pumping rates to effect recombination of the bloodcomponents. For example, fluid may be pumped into the chamber 500 by thein-process pump PU1 at a first flow rate while the chamber 500 is beingrotated in a clockwise or counterclockwise direction, and then therotation in either direction is repeated at a second flow rate. Thecentrifugal force may be decreased, such as by decreasing the rotorspeed, where more than one flow rate is used.

Another modification includes operating the plasma pump PU2 duringrecombination. Plasma exits the chamber 500 via the plasma outlet 542and is pumped through the cassette 592 into the in-process container594. Simultaneously, the flow at the whole blood inlet 510 is reversedusing the in-process pump PU1 so that fluid from the chamber 500 ispulled from the chamber 500 via the whole blood inlet 510, through thecassette 592, and into the in-process container 594. The fluid in thein-process container 594 is then pumped back into the chamber 500through the whole blood inlet 510 by operation of the cassette 592.Therefore, the fluid components are mixed together outside of thechamber 500 and then re-enter the chamber.

It is further possible to modify the pump ratio between the in-processpump PU1 and the plasma pump PU2 during the collection phase todifferent ratios at different times during the procedure.

In yet another embodiment, a 13-port cassette (e.g., one according tothe foregoing description of the cassettes 28 and 28′) may be employedrather than the 14-port cassette 592. This may be achieved, for example,by collecting and storing platelets using only platelet poor plasma,which allows the non-plasma platelet storage solution container to beomitted, thereby alleviating the need for one cassette port. Othermodifications are also possible.

IX. Red Blood Cell and Plasma Collection with Enhanced Functionality

Another benefit of a disposable set incorporating a 14-port cassette isthat it can be used to provide enhanced functionality to procedurestypically carried out with a 13-port cassette. For example, FIG. 65illustrates a disposable set 620 with a 13-port cassette 622 that issuitable for use in practicing the previously described red blood celland plasma collection process. The disposable set 620 is adequate whenthere is no need to filter the collected plasma, such as for proceduresthat are carried out in the United States. However, European standardsfor plasma purity are higher than in the United States, and it isadvantageous to filter the collected plasma to remove cellular bloodcomponents (particularly white blood cells). Hence, a disposable set 624(FIG. 66) incorporating a 14-port cassette 592 may be provided. Theadditional port allows for the inclusion of tubing leading to an in-linefilter 626, a gas exhaust or air burp bag 628, and a pair of plasmastorage containers 630. It will be seen that the disposable set 624 issimilar to the sets illustrated in FIGS. 47 and 48, differingprincipally in the omission of a platelet collection container and aplatelet storage solution container, and the inclusion of theaforementioned filter 626, air burp bag 628, and storage containers 630associated with cassette port PO11. However, the disposable set 624 ofFIG. 66 may be provided with a platelet collection container or othercontainer associated with port PO4 without departing from the scope ofthe present disclosure.

A. Draw Stage

In an exemplary procedure for harvesting red blood cells and plasmausing the disposable set 624 of FIG. 66 (in combination with a suitableblood processing device, such as the one illustrated in FIG. 1), wholeblood is pumped from a blood source to a separation device (e.g., thechamber 500 of FIGS. 44-46) and the in-process container 594.Anticoagulant from the anticoagulant container 562 is added to the wholeblood by operation of the anticoagulant pump PU5 of the cassette 592.The anticoagulated blood may flow into the chamber 500 either from theblood source, or may flow from the in-process container 594, where theblood from the blood source is temporarily stored for subsequentprocessing by the chamber 500. The draw procedure can be understood withfurther reference to the flow diagrams illustrated in FIGS. 52A and 52Band the corresponding description from above.

B. Separation and Collection Stage

Next, within the chamber 500, the fluid components are separated basedon density, as shown in FIG. 46, while the chamber spins at a “hardspin” rate of, for example, approximately 4500 RPM. As the interface 554is pooling upstream of the barrier 516, fluid may be collectedseparately from either side of the interface—or both sidesthereof—through the respective outlet 542 or 544 depending on therequirements of the procedure. For example, in one embodiment(corresponding generally to the flow diagram of FIG. 53 and theaccompanying description from above), some platelet poor plasma 550 iscollected radially inward of the interface 554 through the plasma outlet542 and into the plasma collection container 576. Simultaneously, somered blood cells 552 are collected radially outward of the interface 554through the red blood cell outlet 544 and flow into the red blood cellcollection container 578.

1. Reactive Spill Prevention And Control

In one embodiment, the plasma collection rate is determined by theoperating rate of the plasma pump PU2 of the cassette 592. The operatingrate of the plasma pump PU2 may be constantly ramped to bias the systemtoward an overspill condition. This may be advantageous because anoverspill condition can typically be corrected more quickly than anunderspill condition. In particular, an overspill condition can becorrected by stopping the plasma pump PU2, thereby placing the red bloodcell outlet 544 of the chamber 500 in a “flow-through” condition (inwhich any fluid exiting the chamber 500 does so through the red bloodcell outlet 544 and not the plasma outlet 542) until a calculated volumeof blood has been pumped into the chamber 500. Thereafter, the fluid inthe plasma and red blood cell outlets 542 and 544 may be recirculatedback into the chamber 500 (by operation of the in-process pump PU1) toflush the associated outlet tubing lines of undesirable material.

In contrast, an underspill condition can be corrected by closing the redblood cell outlet 544 and operating the plasma pump PU2 in a“flow-through” state (in which any fluid exiting the chamber 500 does sothrough the plasma outlet 542 and not the red blood cell outlet 544)until a set volume of blood has been pumped into the chamber 500 or anoverspill condition is detected. The underspill condition is finallycorrected by opening the red blood cell outlet 544 and operating theplasma pump PU2 at a lower rate until a set volume of fluid has flownthrough the red blood cell outlet 544 or an overspill condition isdetected.

If the plasma is deemed to be lipemic, it may be advantageous to insteadoperate the plasma pump PU2 at a constantly decreasing rate to bias thesystem toward an underspill condition. Such bias protects the collectedplasma product from platelet contamination, as it may be difficult forthe optical sensor associated with the plasma outlet line to distinguishbetween platelets and lipemic plasma.

2. Predictive Spill Prevention and Control

In an alternative embodiment, the hematocrit of the fluid exiting thered blood cell outlet 544 may be monitored by an optical sensor. Thehematocrit is indicative of the radial location of the interface 554, sothe detected hematocrit may be employed to assess the location of theinterface 554 and change the chamber spin speed to avoid a spillcondition. For example, if the detected hematocrit is greater than aparticular value, it is an indication that the red blood cell layer inthe chamber 500 is too thick, which may create the risk of an overspillcondition. On the other hand, if the detected hematocrit is less than aparticular value, it is an indication that the red blood cell layer inthe chamber 500 is too thin, which may create the risk of an underspillcondition. Increasing the chamber spin speed moves the interface 554closer toward the high-g wall 504 (for responding to a high hematocritreading and avoiding an overspill) while decreasing the chamber spinspeed moves the interface 554 closer toward the low-g wall 502 (forresponding to a low hematocrit reading and avoiding an underspill).

The reactive and predictive spill control systems may also be practicedtogether, for example, with the detected hematocrit being the primarymeans of controlling the location of the interface 554 and the biasedpumping system being used as a back-up.

C. Return Stage

The separation and collection stage typically will continue until thedesired amount of plasma and red blood cells have been collected or arepresent in the system. For example, in one embodiment, the amount of redblood cells includes the packed red cells in the red blood cellcollection container 578, the red blood cells present in the whole bloodremaining in the in-process container 594, and the red blood cells inthe chamber 500 that have yet to be collected.

Depending on the target yields, the target amount of one component(typically red blood cells) may be present in the system before thetarget amount of the other component (typically plasma) has beencollected, so the duration of the separation and collection stage willbe determined by the time required to collect one of the components. Inthe event that the target volume of one of the components (e.g., redblood cells) is obtained before the other (or is expected to be obtainedbefore the other), that component may be periodically returned to theblood source during the separation and collection stage. Mostadvantageously, such return phase is carried out while blood is beingpumped from the in-process container 594 to the chamber 500, asdescribed above with regard to the Red Blood Cell/Platelet/Plasmacollection procedure, to allow for simultaneous processing and fluidreturn.

D. Final Return and Collection Stage

With the target amounts of red blood cells and plasma present in thesystem, the system may move into a final return and collection stage. Inone embodiment, any plasma remaining in the chamber 500 is firstreturned to the blood source. This is achieved by maintaining thechamber at a “hard spin” speed while operating the in-process pump PU1to convey blood from the in-process container 594, through the cassetteflow circuit 600 (in through port PO1 and out through port PO5), andinto the chamber 500 via the whole blood inlet 510, as shown in FIG.67A. The blood entering the chamber 500 forces plasma out of the plasmaoutlet 542, into the cassette flow circuit 600 via port PO6, and thenout cassette port PO8 to the blood source by operation of the plasmapump PU2 and the donor pumps PU3 and PU4.

Returning the plasma to the blood source has the effect of moving theinterface closer to the low-g wall 502 of the chamber 500. To return theinterface layer to the blood source, the spin speed of the chamber 500is reduced while the in-process pump PU1 continues to convey blood fromthe in-process container 594, through the cassette flow circuit 600 (inthrough port PO1 and out through port PO5), and into the chamber 500 viathe inlet 510, as shown in FIG. 67A. At the lower spin speed, theinterface will be close to the low-g wall 502, so the blood entering thechamber 500 forces the interface out of the plasma outlet 542, throughthe cassette flow circuit 600 (in through port PO6 and out through portPO8), and to the blood source by operation of the plasma pump PU2 andthe donor pumps PU3 and PU4. This “flush interface” phase continuesuntil the in-process container 594 falls below a set volume, as may bedetermined by a weight sensor associated with the in-process container594. In one embodiment, the “flush interface” phase continues until thein-process container 594 is empty.

When the interface has been flushed from the chamber 500, the volume ofpacked red cells in the red blood cell collection container 578 isassessed to determine whether there are any excess red blood cells inthe system. If so, the in-process pump PU1 is stopped, while the plasmapump PU2 and the donor pumps PU3 and PU4 continue to operate, therebypulling some packed red cells from the red blood cell collectioncontainer 578, through the cassette flow circuit 600 (in through portPO2 and out through port PO7), and into the chamber 500 via the redblood cell outlet 544, as shown in FIG. 67B. The red blood cellsentering the chamber 500 force excess red blood cells in the chamber 500out the plasma outlet 542, though the cassette flow circuit 600 (inthrough port PO6 and out through port PO8), to be returned to the bloodsource. It will be appreciated that the hematocrit of the packed redcells entering the chamber 500 from the red blood cell collectioncontainer 578 is greater than that of the red blood cells exiting thechamber 500, thereby effectively increasing the hematocrit of the fluidin the chamber 500.

Next, the volume of plasma in the plasma collection container 576 isassessed to determine whether there is any excess plasma in the system.If so, the plasma pump PU2 is stopped, while the donor pumps PU3 and PU4continue to operate, and the flow path through the cassette 592 ismodified to direct any excess plasma from the plasma collectioncontainer 576, through the cassette flow circuit 600 (in through portPO3 and out through port PO8), and to the blood source, entirelybypassing the chamber 500 to avoid lowering the hematocrit of the fluidtherein. This phase is illustrated in FIG. 67C. The blood source may bedisconnected from the system at this time.

Next, air from the empty in-process container 594 is pumped through thecassette flow circuit 600 (in through port PO1 and out through port PO5)and into the chamber 500 by the in-process pump PU1, as shown in FIG.67D. The valves VAL17 and VAL19 associated with the plasma outlet portPO6 are closed, thereby causing the air entering the chamber 500 toforce the red blood cells therein out the red blood cell outlet 544,through the cassette flow circuit 600 (in through port PO7 and outthrough port PO2), and to the red blood cell collection container 578.This phase continues until the red blood cells in the chamber 500 havebeen conveyed to the red blood cell collection container 578, which maybe identified when the weight sensor associated with the red blood cellcollection container 578 stops registering an increase in volume.

When the red blood cells have been conveyed from the chamber 500 to thered blood cell collection container 578, the valve VAL21 associated withthe red blood cell outlet port PO7 is closed and valve VAL17 is opened,thereby effectively re-opening the plasma outlet port PO6, as shown inFIG. 67E. Air is still being pumped into the chamber 500 from thein-process container 594, and the air pumped through the chamber 500 isdirected out the plasma outlet 542 and associated plasma outlet portPO6, thereby flushing any red blood cells in the plasma pump PU2 oroutlet line to the red blood cell collection container 578 (via portPO2) and completing collection of the red blood cells. If the bloodsource is still attached to the system, saline from a saline containermay be pumped to the blood source to flush any blood components in thereturn line (typically red blood cells) to the blood source, and thenthe blood source is finally disconnected from the system.

E. Flush Stage

The above final return and collection stage may be replaced by aconditional “flush” stage that is employed if the collection procedureis stopped prematurely or otherwise interrupted.

The “flush” stage operates to return fluid to the blood source. In oneembodiment, the chamber spin speed is ramped down to zero while bloodfrom the in-process container 594 is conveyed to the blood source andexcess red blood cells and plasma are returned from their respectivecollection container, with the material being returned using the donorpumps PU3 and PU4 of the cassette 592. Most advantageously, the contentsof the containers are returned to the blood source while bypassing thechamber 500, which can be achieved by properly programming the valvesVAL1-VAL26 of the cassette 592. If the plasma or red blood cell level isbelow the target volume (e.g., if the procedure was stoppedprematurely), the operator may be given the option to convey the entirecontents of the associated collection container to the blood source.Alternatively, the system may attempt to salvage some of the componentsby retaining an amount less than the target volume, such as by retainingone unit of a component after an interruption prevents collection of thetargeted two units.

When the chamber 500 has stopped spinning, the system moves to an “airflush” phase to begin flushing any excess fluid remaining in the systemto the blood source. In this phase, the in-process pump PU1 conveys airfrom the in-process container 594, through the cassette flow circuit 600(in through port PO1 and out through port PO5), and into the chamber 500(FIG. 68). The air forces some (about half) of the contents of thechamber 500 out of the red blood cell outlet 544, through the cassetteflow circuit 600 (entering via port PO7), before the donor pumps PU3 andPU4 are operated to return the flushed contents to the blood source (viaport PO8).

Next, the various pumps are stopped and the chamber spin speed isincreased to a “flush chamber” speed of, for example, about 1000 RPM.When the spin speed has reached the target level, the above “air flush”phase (FIG. 68) is repeated to flush more of the contents of the chamber500 to the blood source. This may be followed by a “saline return”stage, whereby the donor pumps PU3 and PU4 of the cassette 592 pumpsaline from a saline container (not illustrated) to the blood source,thereby flushing cells in the tubing back to the blood source.

However, if the contents of the plasma collection container 576 werepreviously returned to the blood source (e.g., when the decision hasbeen made to not salvage any of the collected plasma), the “salinereturn” stage may be preceded by an additional “air flush” phase. Such athird “air flush” phase is illustrated in FIGS. 69A-69C. First, theabove “air flush” phase is repeated, with the contents of the chamber500 being flushed through the cassette flow circuit 600 (in through portPO7 and out through port PO3) to the plasma collection container 576,rather than being returned to the blood source (FIG. 69A). Thisadditional “air flush” phase substantially empties the chamber 500.

Next, saline is pumped from a saline container, through the cassetteflow circuit 600 (in through port PO13 and out through port PO3), andinto the plasma collection container 576 to prime the flow path to theplasma collection container 576 (FIG. 69B).

Finally, the contents of the plasma collection container 576 are pumpedthrough the cassette flow circuit 600 (in through port PO3 and outthrough port PO8) and returned to the blood source (FIG. 69C).Thereafter, the blood source may be disconnected from the system.

F. Filtration Stage

If at least one of the collected components (i.e., plasma or packed redcells) is being retained, the final return and collection of the “flush”stage may be followed by a leukoreduction stage. As shown in FIG. 66,the disposable set 624 may include a red blood cell storage container586 and at least one plasma storage container 630. Each storagecontainer includes an associated in-line leukoreduction filter 590/626,such that the component is filtered as it is pumped from the collectioncontainer to the storage container by the cassette 592. Theleukoreduction of the packed red cells and/or plasma can be understoodwith reference to the corresponding stage of the Red BloodCell/Platelet/Plasma collection procedure, described above.

X. Other Blood Processing Functions

The many features of the present subject matter have been demonstratedby describing their use in separating whole blood into component partsfor storage and blood component therapy. This is because the presentsubject matter is well adapted for use in carrying out these bloodprocessing procedures. It should be appreciated, however, that thedescribed features equally lend themselves to use in other bloodprocessing procedures.

For example, the systems and methods described, which make use of aprogrammable cassette in association with a blood processing chamber,can be used for the purpose of washing or salvaging blood cells duringsurgery, or for the purpose of conducting therapeutic plasma exchange,or in any other procedure where blood is circulated in an extracorporealpath for treatment.

It will be understood that the embodiments described above areillustrative of some of the applications of the principles of thepresent subject matter. Numerous modifications may be made by thoseskilled in the art without departing from the spirit and scope of theclaimed subject matter, including those combinations of features thatare individually disclosed or claimed herein. For these reasons, thescope hereof is not limited to the above description but is as set forthin the following claims.

1. A blood separation method comprising: processing blood in a device toseparate a blood component from the blood; conveying fluid containingsaid blood component from the device by an outlet line; opticallymeasuring the blood component in the outlet line; calculating a bloodcomponent pre-count, based at least in part on the optical measurementof the blood component in the outlet line; ceasing said calculating; andprocessing additional blood in the device after ceasing said calculatingwherein said blood component is platelets.
 2. The method of claim 1,further comprising reducing the amount of plasma in the device, whileretaining substantially all of the platelets in the device, prior tosaid conveying fluid containing said blood component from the device bythe outlet line.
 3. The method of claim 1, wherein said conveying fluidcontaining said blood component from the device by the outlet linecomprises circulating a fluid containing platelets from the devicethrough the outlet line and then back into the device, and wherein saidoptically measuring includes optically measuring the platelets in theoutlet line while simultaneously circulating the fluid containingplatelets from the device through the outlet line and then back into thedevice.
 4. A blood separation method comprising: processing blood in adevice to separate platelets from the blood; circulating a fluidcontaining platelets from the device through an outlet line and thenback into the device while simultaneously optically measuring theplatelets in the outlet line; calculating a current platelet yield, aplatelet pre-count, the volume of blood to process to collect a targetamount of platelets, and/or the processing time required to collect atarget amount of platelets, based at least in part on the opticalmeasurement of the platelets in the outlet line; ceasing saidcalculating; and processing additional blood in the device after ceasingsaid calculating, wherein said circulating the fluid containingplatelets from the device through the outlet line and then back into thedevice is repeated until the fluid containing platelets is substantiallyuniform.
 5. A blood separation method comprising: processing blood in adevice to separate platelets from the blood; conveying fluid containingplatelets from the device by an outlet line; optically measuring theplatelets in the outlet line; calculating a current platelet yield, aplatelet pre-count, the volume of blood to process to collect a targetamount of platelets, and/or the processing time required to collect atarget amount of platelets, based at least in part on the opticalmeasurement of the platelets in the outlet line; ceasing saidcalculating; and processing additional blood in the device after ceasingsaid calculating, wherein said processing blood in a device includesspinning the device to separate platelets from the blood, and saidcalculating a current platelet yield includes comparing the calculatedplatelet yield to a target and, if the calculated platelet yield exceedsthe target, spinning the device at a greater speed to reduce the amountof platelets in the outlet line or, if the calculated platelet yieldfalls below the target, spinning the device at a slower speed toincrease the amount of platelets in the outlet line.
 6. The method ofclaim 1, further comprising conveying separated platelets and an amountof platelet storage fluid to a platelet collection container, whereinsaid amount of platelet storage fluid is based, at least in part, on theoptical measurement of the platelets in the outlet line.
 7. A bloodseparation method comprising: processing blood in a device having afirst outlet line and a second outlet line to separate platelets fromthe blood; conveying fluid containing platelets from the device by anoutlet line; optically measuring the platelets in the outlet line;calculating a current platelet yield, a platelet pre-count, the volumeof blood to process to collect a target amount of platelets, and/or theprocessing time required to collect a target amount of platelets, basedat least in part on the optical measurement of the platelets in theoutlet line; ceasing said calculating; and processing additional bloodin the device after ceasing said calculating, wherein said processingblood in a device comprises spinning the device at a separation speedsufficient to separate the blood in the device into a red blood celllayer, a plasma layer, and a layer containing platelets; conveying aflow of the separated plasma from the device through one of the outletlines and conveying a flow of the separated red blood cells from thedevice through the other outlet line, while retaining substantially allof the layer containing platelets in the device; spinning the device inalternating directions at a relatively low mixing speed to mix theseparated plasma, the separated red blood cells, and the layercontaining platelets remaining in the device; and spinning the device ata harvest speed that is less than the separation speed to separate themixed plasma, red blood cells, and layer containing platelets into alayer of red blood cells and a layer containing plasma and platelets;said conveying fluid containing platelets from the device by the outletline comprises circulating the layer containing plasma and plateletsfrom the device through the first outlet line and then back into thedevice to reduce the number of red blood cells and leukocytes in thelayer containing plasma and platelets; and said optically measuring theplatelets in the outlet line comprises optically measuring the plateletsin the first outlet line while simultaneously circulating the layercontaining plasma and platelets from the device through the first outletline and then back into the device.
 8. The method of claim 7, whereinsaid circulating the layer containing plasma and platelets from thedevice through the first outlet line and then back into the device isrepeated until the layer containing plasma and platelets issubstantially uniform.
 9. The method of claim 7, wherein saidcalculating a current blood component yield includes comparing thecalculated blood component yield to a target and, if the calculatedblood component yield exceeds the target, spinning the device at agreater speed to reduce the amount of platelets in the first outlet lineor, if the calculated blood component yield falls below the target,spinning the device at a slower speed to increase the amount ofplatelets in the first outlet line.
 10. The method of claim 7, furthercomprising conveying separated platelets and an amount of plateletstorage fluid to a platelet collection container, wherein said amount ofplatelet storage fluid is based, at least in part, on the opticalmeasurement of the platelets in the first outlet line.